EP2890431B1 - Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament - Google Patents

Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament Download PDF

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Publication number
EP2890431B1
EP2890431B1 EP13762335.1A EP13762335A EP2890431B1 EP 2890431 B1 EP2890431 B1 EP 2890431B1 EP 13762335 A EP13762335 A EP 13762335A EP 2890431 B1 EP2890431 B1 EP 2890431B1
Authority
EP
European Patent Office
Prior art keywords
drug
drive mechanism
tether
status
piston
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Not-in-force
Application number
EP13762335.1A
Other languages
German (de)
English (en)
Other versions
EP2890431A2 (fr
Inventor
Ian B. Hanson
Paul F. Bente, Iv
Kevin Bokelman
John C. Love
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Unitract Syringe Pty Ltd
Original Assignee
Unitract Syringe Pty Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Unitract Syringe Pty Ltd filed Critical Unitract Syringe Pty Ltd
Priority to EP17162587.4A priority Critical patent/EP3225265A1/fr
Priority to EP16151332.0A priority patent/EP3028727B1/fr
Priority to DK16151332.0T priority patent/DK3028727T3/en
Publication of EP2890431A2 publication Critical patent/EP2890431A2/fr
Application granted granted Critical
Publication of EP2890431B1 publication Critical patent/EP2890431B1/fr
Not-in-force legal-status Critical Current
Anticipated expiration legal-status Critical

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A61M5/14546—Front-loading type injectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A61M5/1454—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons spring-actuated, e.g. by a clockwork
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A61M5/14566—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons with a replaceable reservoir for receiving a piston rod of the pump
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16804—Flow controllers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/172—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M2005/14208—Pressure infusion, e.g. using pumps with a programmable infusion control system, characterised by the infusion program
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
    • A61M5/14248—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body of the skin patch type
    • A61M2005/14252—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body of the skin patch type with needle insertion means
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/0007—Special media to be introduced, removed or treated introduced into the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate

Definitions

  • THIS INVENTION relates to drug delivery pumps. More particularly, this invention relates to drive mechanisms for the controlled delivery of drug substances, drug delivery pumps with controlled delivery drive mechanisms, the methods of operating such devices, and the methods of assembling such devices.
  • Parenteral delivery of various drugs i.e., delivery by means other than through the digestive track, has become a desired method of drug delivery for a number of reasons.
  • This form of drug delivery by injection may enhance the effect of the substance being delivered and ensure that the unaltered medicine reaches its intended site at a significant concentration.
  • undesired side effects associated with other routes of delivery such as systemic toxicity, can potentially be avoided through parenteral delivery.
  • By bypassing the digestive system of a mammalian patient one can avoid degradation of the active ingredients caused by the catalytic enzymes in the digestive tract and liver and ensure that a necessary amount of drug, at a desired concentration, reaches the targeted site.
  • parenteral delivery of liquid medicines into the body has been accomplished by administering bolus injections using a needle and reservoir, continuously by gravity driven dispensers, or via transdermal patch technologies.
  • Bolus injections often imperfectly match the clinical needs of the patient, and usually require larger individual doses than are desired at the specific time they are given.
  • Continuous delivery of medicine through gravity-feed systems compromises the patient's mobility and lifestyle, and limits the therapy to simplistic flow rates and profiles.
  • Another form of drug delivery, transdermal patches similarly has its restrictions. Transdermal patches often require specific molecular drug structures for efficacy, and the control of the drug administration through a transdermal patch is severely limited.
  • Ambulatory infusion pumps have been developed for delivering liquid medicaments to a patient. These infusion devices have the ability to offer sophisticated fluid delivery profiles accomplishing bolus requirements, continuous infusion and variable flow rate delivery. These infusion capabilities usually result in better efficacy of the drug and therapy and less toxicity to the patient's system.
  • ambulatory infusion devices are expensive, difficult to program and prepare for infusion, and tend to be bulky, heavy and very fragile. Filling these devices can be difficult and require the patient to carry both the intended medication as well as filling accessories. The devices often require specialized care, maintenance, and cleaning to assure proper functionality and safety for their intended long-term use, and are not cost-effective for patients or healthcare providers.
  • pump type delivery devices can be significantly more convenient to a patient, in that doses of the drug may be calculated and delivered automatically to a patient at any time during the day or night.
  • pumps may be automatically controlled to provide appropriate doses of a fluidic medium at appropriate times of need, based on sensed or monitored metabolic levels.
  • pump type delivery devices have become an important aspect of modem medical treatments of various types of medical conditions, such as diabetes, and the like.
  • WO2008142394A1 discloses an infusion pump for administering controlled doses of a fluid.
  • this document does not disclose the claimed arrangement including, for example, the status reader disposed adjacent the tether, the status reader being configured to provide a signal when slack occurs in the tether.
  • this document does not disclose the claimed arrangement including a gear assembly including a plurality of gears wherein at least one of said gears is configured to act as an encoder, or a compound gear engageably connected to the worm gear.
  • this document also does not disclose status triggers incrementally spaced on the tether, wherein, during operation of the drive mechanism, interaction between the status reader and the status triggers transmit a signal to a power and control system to provide feedback to a user.
  • Embodiments of present invention provides drive mechanisms for the controlled delivery of drug substances, drug delivery pumps with controlled delivery drive mechanisms, the methods of operating such devices, and the methods of assembling such devices.
  • the drive mechanisms of embodiments of the present invention control the rate of drug delivery by metering, providing resistance, or otherwise preventing free axial translation of the plunger seal utilized to force a drug substance out of a drug container.
  • the novel embodiments of the present invention thus are capable of delivering drug substances at variable rates.
  • the controlled delivery drive mechanisms of embodiments of the present invention may be pre-configurable or dynamically configurable, such as by control by the power and control system, to meet desired delivery rates or profiles, as explained in detail below.
  • the drive mechanisms of embodiments of the present invention provide integrated status indication features which provide feedback to the user before, during, and after drug delivery.
  • the user may be provided an initial feedback to identify that the system is operational and ready for drug delivery.
  • the system may then provide one or more drug delivery status indications to the user.
  • the drive mechanism and drug pump may provide an end-of-dose indication. Because the end-of-dose indication is related to the physical end of axial translation of one or more components of the drive mechanism, the drive mechanism and drug pump provide a true end-of-dose indication to the user.
  • the novel devices of embodiments of the present invention alleviate one or more of the problems associated with prior art devices, such as those referred to above.
  • the present invention provides a controlled delivery drive mechanism which includes a drive housing, a piston, and a biasing member, wherein the biasing member is initially retained in an energized state and is configured to bear upon an interface surface of the piston.
  • the piston is configured to translate substantially axially within a drug container having a plunger seal and a barrel.
  • a tether is connected at one end to the piston and at another end to a winch drum of a delivery control mechanism, wherein the tether restrains the free expansion of the biasing member from its initial energized state and the free axial translation of the piston upon which the biasing member bears upon.
  • the drug container may contain a drug fluid within a drug chamber for delivery to a user.
  • a cover sleeve may be utilized between the biasing member and the interface surface of the piston to hide the interior components of the barrel (namely, the piston and the biasing member) from view during operation of the drive mechanism.
  • the tether is configured to be released from a winch drum of the delivery control mechanism to meter the free expansion of the biasing member from its initial energized state and the free axial translation of the piston upon which the biasing member bears upon.
  • the drive mechanism further includes a gear assembly.
  • the gear assembly may include a winch gear connected to a winch drum upon which the tether may be releasably wound, a worm gear engageably connected to the winch gear, a compound gear engageably connected to the worm gear, and a motor having a pinion engageably connected to the compound gear, wherein the motor is configured to drive the gear assembly to release the tether from the winch drum to meter the free expansion of the biasing member from its initial energized state and the free axial translation of the piston upon which the biasing member bears upon.
  • the metering of the tether by the motor controls the rate or profile of drug delivery to a user.
  • the piston may be one or more parts and connects to a distal end of the tether.
  • the drive mechanism may include a status reader configured to read or recognize one or more corresponding status triggers.
  • the status triggers may be incrementally spaced on the tether, wherein, during operation of the drive mechanism, interaction between the status reader and the status triggers transmit a signal to a power and control system to provide feedback to a user.
  • the status reader may be an optical status reader and the corresponding status triggers are optical status triggers, an electromechanical status reader and the corresponding status triggers are electromechanical status triggers, or a mechanical status reader and the corresponding status triggers are mechanical status triggers.
  • the present invention provides a drug delivery pump with controlled drug delivery.
  • the drug having a housing and an assembly platform, upon which an activation mechanism, an insertion mechanism, a fluid pathway connection, a power and control system, and a controlled delivery drive mechanism may be mounted, said drive mechanism having a drive housing, a piston, and a biasing member, wherein the biasing member is initially retained in an energized state and is configured to bear upon an interface surface of the piston.
  • the piston is configured to translate substantially axially within a drug container having a plunger seal and a barrel.
  • a tether is connected at one end to the piston and at another end to a winch drum of a delivery control mechanism, wherein the tether restrains the free expansion of the biasing member from its initial energized state and the free axial translation of the piston upon which the biasing member bears upon.
  • the drug container may contain a drug fluid within a drug chamber for delivery to a user.
  • a cover sleeve may be utilized between the biasing member and the interface surface of the piston to hide the interior components of the barrel (namely, the piston and the biasing member) from view during operation of the drive mechanism.
  • the tether is configured to be released from a winch drum of the delivery control mechanism to meter the free expansion of the biasing member from its initial energized state and the free axial translation of the piston upon which the biasing member bears upon.
  • the drug pump further includes a gear assembly.
  • the gear assembly may include a winch gear connected to a winch drum upon which the tether may be releasably wound, a worm gear engageably connected to the winch gear, a compound gear engageably connected to the worm gear, and a motor having a pinion engageably connected to the compound gear, wherein the motor is configured to drive the gear assembly to release the tether from the winch drum to meter the free expansion of the biasing member from its initial energized state and the free axial translation of the piston upon which the biasing member bears upon.
  • the metering of the tether by the motor controls the rate or profile of drug delivery to a user.
  • the piston may be one or more parts and connects to a distal end of the tether.
  • the drug pump may include a status reader configured to read or recognize one or more corresponding status triggers.
  • the status triggers may be incrementally spaced on the tether, wherein, during operation of the drive mechanism, interaction between the status reader and the status triggers transmit a signal to a power and control system to provide feedback to a user.
  • the status reader may be an optical status reader and the corresponding status triggers are optical status triggers, an electromechanical status reader and the corresponding status triggers are electromechanical status triggers, or a mechanical status reader and the corresponding status triggers are mechanical status triggers.
  • the power and control system of the drug pump is configured to receive one or more inputs to meter the release of the tether by the winch drum and thereby permit axial translation of the piston by the biasing member to translate a plunger seal within a barrel.
  • the one or more inputs may be provided by the actuation of the activation mechanism, a control interface, and/or a remote control mechanism.
  • the power and control system may be configured to receive one or more inputs to adjust the restrain provided by the tether and winch drum on the free axial translation of the piston upon which the biasing member bears upon to meet a desired drug delivery rate or profile, to change the dose volume for delivery to the user, and/or to otherwise start, stop, or pause operation of the drive mechanism.
  • novel embodiments of the present invention provide drive mechanisms which are capable of metering, providing resistance, or otherwise preventing free axial translation of the plunger seal utilized to force a drug substance out of a drug container and, thereby, controlling the rate of delivery of drug substances.
  • the novel control delivery drive mechanisms are additionally capable of providing the incremental status of the drug delivery before, during, and after operation of the device.
  • the embodiments of the present invention may include one or more additional components which may be considered standard components in the industry of medical devices.
  • the embodiments may include one or more batteries utilized to power the motor, drive mechanisms, and drug pumps of embodiments of the present invention.
  • Embodiments of the present invention provide drive mechanisms for the controlled delivery of drug substances and drug delivery pumps which incorporate such controlled delivery drive mechanisms.
  • the drive mechanisms of embodiments of the present invention control the rate of drug delivery by metering, providing resistance, or otherwise preventing free axial translation of the plunger seal utilized to force a drug substance out of a drug container and, thus, are capable of delivering drug substances at variable rates and/or delivery profiles.
  • the drive mechanisms of embodiments of the present invention provide integrated status indication features which provide feedback to the user before, during, and after drug delivery. For example, the user may be provided an initial feedback to identify that the system is operational and ready for drug delivery. Upon activation, the system may then provide one or more drug delivery status indications to the user. At completion of drug delivery, the drive mechanism and drug pump may provide an end-of-dose indication.
  • the terms “axial” or “axially” refer generally to a longitudinal axis "A” around which the drive mechanisms are preferably positioned, although not necessarily symmetrically there-around.
  • the term “radial” refers generally to a direction normal to axis A.
  • proximal,” “rear,” “rearward,” “back,” or “backward” refer generally to an axial direction in the direction “P”.
  • distal refer generally to an axial direction in the direction "D”.
  • glass should be understood to include other similarly non-reactive materials suitable for use in a pharmaceutical grade application that would normally require glass, including but not limited to certain non-reactive polymers such as cyclic olefin copolymers (COC) and cyclic olefin polymers (COP).
  • non-reactive polymers such as cyclic olefin copolymers (COC) and cyclic olefin polymers (COP).
  • COC cyclic olefin copolymers
  • COP cyclic olefin polymers
  • the term "plastic” may include both thermoplastic and thermosetting polymers. Thermoplastic polymers can be resoftened to their original condition by heat; thermosetting polymers cannot.
  • plastic refers primarily to moldable thermoplastic polymers such as, for example, polyethylene and polypropylene, or an acrylic resin, that also typically contain other ingredients such as curatives, fillers, reinforcing agents, colorants, and/or plasticizers, etc., and that can be formed or molded under heat and pressure.
  • plastic is not meant to include glass, non-reactive polymers, or elastomers that are approved for use in applications where they are in direct contact with therapeutic liquids that can interact with plastic or that can be degraded by substituents that could otherwise enter the liquid from plastic.
  • elastomer refers primarily to cross-linked thermosetting rubbery polymers that are more easily deformable than plastics but that are approved for use with pharmaceutical grade fluids and are not readily susceptible to leaching or gas migration under ambient temperature and pressure.
  • Fluid refers primarily to liquids, but can also include suspensions of solids dispersed in liquids, and gasses dissolved in or otherwise present together within liquids inside the fluid-containing portions of the drug pumps. According to various aspects and embodiments described herein, reference is made to a "biasing member”, such as in the context of one or more biasing members for asserting force on a plunger seal.
  • the biasing member may be any member that is capable of storing and releasing energy.
  • Non-limiting examples include a spring, such as for example a coiled spring, a compression or extension spring, a torsional spring, or a leaf spring, a resiliently compressible or elastic band, or any other member with similar functions.
  • the biasing member is a spring, preferably a compression spring.
  • novel devices of embodiments of the present invention provide drive mechanisms with integrated status indication and drug delivery pumps which incorporate such drive mechanisms. Such devices are safe and easy to use, and are aesthetically and ergonomically appealing for self-administering patients.
  • the devices described herein incorporate features which make activation, operation, and lock-out of the device simple for even untrained users.
  • the novel devices of embodiments of the present invention provide these desirable features without any of the problems associated with known prior art devices. Certain non-limiting embodiments of the novel drug delivery pumps, drive mechanisms, and their respective components are described further herein with reference to the accompanying figures.
  • FIGS. 1A-1C show an exemplary drug delivery device according to at least one embodiment of the present invention.
  • the drug delivery device may be utilized to administer delivery of a drug treatment into a body of a user.
  • the drug pump 10 includes a pump housing 12.
  • Pump housing 12 may include one or more housing subcomponents which are fixedly engageable to facilitate easier manufacturing, assembly, and operation of the drug pump.
  • drug pump 10 includes a pump housing 12 which includes an upper housing 12A and a lower housing 12B.
  • the drug pump may further include an activation mechanism 14, a status indicator 16, and a window 18.
  • Window 18 may be any translucent or transmissive surface through which the operation of the drug pump may be viewed.
  • drug pump further includes assembly platform 20, sterile fluid conduit 30, drive mechanism 100 having drug container 50, insertion mechanism 200, fluid pathway connection 300, and power and control system 400.
  • One or more of the components of such drug pumps may be modular in that they may be, for example, pre-assembled as separate components and configured into position onto the assembly platform 20 of the drug pump 10 during manufacturing.
  • the pump housing 12 contains all of the device components and provides a means of removably attaching the device 10 to the skin of the user.
  • the pump housing 12 also provides protection to the interior components of the device 10 against environmental influences.
  • the pump housing 12 is ergonomically and aesthetically designed in size, shape, and related features to facilitate easy packaging, storage, handling, and use by users who may be untrained and/or physically impaired.
  • the external surface of the pump housing 12 may be utilized to provide product labeling, safety instructions, and the like.
  • housing 12 may include certain components, such as status indicator 16 and window 18, which may provide operation feedback to the user.
  • the drug pump 10 provides an activation mechanism 14 that is displaced by the user to trigger the start command to the power and control system 400.
  • the activation mechanism is a start button 14 that is located through the pump housing 12, such as through an aperture between upper housing 12A and lower housing 12B, and which contacts a control arm 40 of the power and control system 400.
  • the start button 14 may be a push button, and in other embodiments, may be an on/off switch, a toggle, or any similar activation feature known in the art.
  • the pump housing 12 also provides a status indicator 16 and a window 18.
  • one or more of the activation mechanism 14, the status indicator 16, the window 18, and combinations thereof may be provided on the upper housing 12A or the lower housing 12B such as, for example, on a side visible to the user when the drug pump 10 is placed on the body of the user.
  • Housing 12 is described in further detail hereinafter with reference to other components and embodiments of the present invention.
  • Drug pump is configured such that, upon activation by a user by depression of the activation mechanism, the drug pump is initiated to: insert a fluid pathway into the user; enable, connect, or open necessary connections between a drug container, a fluid pathway, and a sterile fluid conduit; and force drug fluid stored in the drug container through the fluid pathway and fluid conduit for delivery into a user.
  • One or more optional safety mechanisms may be utilized, for example, to prevent premature activation of the drug pump.
  • an optional on-body sensor 24 shown in FIG. 1C ) may be provided in one embodiment as a safety feature to ensure that the power and control system 400, or the activation mechanism, cannot be engaged unless the drug pump 10 is in contact with the body of the user.
  • the on-body sensor 24 is located on the bottom of lower housing 12B where it may come in contact with the user's body. Upon displacement of the on-body sensor 24, depression of the activation mechanism is permitted. Accordingly, in at least one embodiment the on-body sensor 24 is a mechanical safety mechanism, such as for example a mechanical lock out, that prevents triggering of the drug pump 10 by the activation mechanism 14. In another embodiment, the on-body sensor may be an electro-mechanical sensor such as a mechanical lock out that sends a signal to the power and control system 400 to permit activation.
  • the on-body sensor can be electrically based such as, for example, a capacitive- or impedance-based sensor which must detect tissue before permitting activation of the power and control system 400.
  • the drug pump 10 utilizes one or more mechanical on-body sensors. Additional integrated safety mechanisms are described herein with reference to other components of the novel drug pumps.
  • the power and control system 400 includes a power source, which provides the energy for various electrical components within the drug pump, one or more feedback mechanisms, a microcontroller, a circuit board, one or more conductive pads, and one or more interconnects. Other components commonly used in such electrical systems may also be included, as would be appreciated by one having ordinary skill in the art.
  • the one or more feedback mechanisms may include, for example, audible alarms such as piezo alarms and/or light indicators such as light emitting diodes (LEDs).
  • the microcontroller may be, for example, a microprocessor.
  • the power and control system 400 controls several device interactions with the user and interfaces with the drive mechanism 100.
  • the power and control system 400 interfaces with the control arm 40 to identify when the on-body sensor 24 and/or the activation mechanism 14 have been activated.
  • the power and control system 400 may also interface with the status indicator 16 of the pump housing 12, which may be a transmissive or translucent material which permits light transfer, to provide visual feedback to the user.
  • the power and control system 400 interfaces with the drive mechanism 100 through one or more interconnects to relay status indication, such as activation, drug delivery, and end-of-dose, to the user.
  • Such status indication may be presented to the user via auditory tones, such as through the audible alarms, and/or via visual indicators, such as through the LEDs.
  • control interfaces between the power and control system and the other components of the drug pump are not engaged or connected until activation by the user. This is a desirable safety feature that prevents accidental operation of the drug pump and may additionally maintain the energy contained in the power source during storage, transportation, and the like.
  • the power and control system 400 may be configured to provide a number of different status indicators to the user.
  • the power and control system 400 may be configured such that after the on-body sensor and/or trigger mechanism have been pressed, the power and control system 400 provides a ready-to-start status signal via the status indicator 16 if device start-up checks provide no errors. After providing the ready-to-start status signal and, in an embodiment with the optional on-body sensor, if the on-body sensor remains in contact with the body of the user, the power and control system 400 will power the drive mechanism 100 to begin delivery of the drug treatment through the fluid pathway connection 300 and sterile fluid conduit 30.
  • the insertion mechanism 200 and the fluid pathway connection 300 may be caused to activate directly by user operation of the activation mechanism 14.
  • the power and control system 400 is configured to provide a dispensing status signal via the status indicator 16. After the drug has been administered into the body of the user and after the end of any additional dwell time, to ensure that substantially the entire dose has been delivered to the user, the power and control system 400 may provide an okay-to-remove status signal via the status indicator 16. This may be independently verified by the user by viewing the drive mechanism and drug dose delivery through the window 18 of the pump housing 12. Additionally, the power and control system 400 may be configured to provide one or more alert signals via the status indicator 16, such as for example alerts indicative of fault or operation failure situations.
  • the power and control system 400 may additionally be configured to accept various inputs from the user to dynamically control the drive mechanisms 100 to meet a desired drug delivery rate or profile.
  • the power and control system 400 may receive inputs, such as from partial or full activation, depression, and/or release of the activation mechanism 14, to set, initiate, stop, or otherwise adjust the control of the drive mechanism 100 via the power and control system 400 to meet the desired drug delivery rate or profile.
  • the power and control system 400 may be configured to receive such inputs to adjust the drug dose volume; to prime the drive mechanism, fluid pathway connection, and fluid conduit; and/or to start, stop, or pause operation of the drive mechanism 100.
  • Such inputs may be received by the user directly acting on the drug pump 10, such as by use of the activation mechanism 14 or a different control interface, or the system 400 may be configured to receive such inputs from a remote control device. Additionally or alternatively, such inputs may be pre-programmed.
  • activation delays may be utilized during drug delivery.
  • one such delay optionally included within the system configuration is a dwell time which ensures that substantially the entire drug dose has been delivered before signaling completion to the user.
  • activation of the device may require a delayed depression (i.e., pushing) of the activation mechanism 14 of the drug pump 10 prior to drug pump activation.
  • the system may include a feature which permits the user to respond to the end-of-dose signals and to deactivate or power-down the drug pump. Such a feature may similarly require a delayed depression of the activation mechanism, to prevent accidental deactivation of the device.
  • An additional safety feature may be integrated into the activation mechanism to prevent partial depression and, therefore, partial activation of the drug pumps.
  • the activation mechanism and/or power and control system may be configured such that the device is either completely off or completely on, to prevent partial activation.
  • a suitable fluid pathway connection includes a sterile fluid conduit, a piercing member, and a sterile sleeve attached to a drug container or a sliding pierceable seal integrated within a drug container.
  • the fluid pathway connection may further include one or more flow restrictors.
  • the fluid pathway connection 300 is enabled to connect the sterile fluid conduit 30 to the drug container of the drive mechanism 100.
  • Such connection may be facilitated by a piercing member, such as a needle, penetrating a pierceable seal of the drug container of the drive mechanism 100.
  • the sterility of this connection may be maintained by performing the connection within a flexible sterile sleeve.
  • the fluid pathway between drug container and insertion mechanism is complete to permit drug delivery into the body of the user.
  • the piercing member of the fluid pathway connection is caused to penetrate the pierceable seal of the drug container of the drive mechanism by direct action of the user, such as by depression of the activation mechanism by the user.
  • the activation mechanism itself may bear on the fluid pathway connection such that displacement of the activation mechanism from its original position also causes displacement of the fluid pathway connection.
  • the fluid pathway connection may be substantially similar to that described in International Patent Application No. PCT/US2012/054861 , which is included by reference herein in its entirety for all purposes.
  • connection is enabled by the user depressing the activation mechanism and, thereby, driving the piercing member through the pierceable seal, because this prevents fluid flow from the drug container until desired by the user.
  • a compressible sterile sleeve may be fixedly attached between the cap of the drug container and the connection hub of the fluid pathway connection.
  • the piercing member may reside within the sterile sleeve until a connection between the fluid connection pathway and the drug container is desired.
  • the sterile sleeve may be sterilized to ensure the sterility of the piercing member and the fluid pathway prior to activation.
  • a drug container may have a drug chamber within a barrel between a pierceable seal and a plunger seal.
  • a drug fluid is contained in the drug chamber.
  • a drive mechanism Upon activation of the device by the user, a drive mechanism asserts a force on a plunger seal contained in the drug container. As the plunger seal asserts a force on the drug fluid and any air/gas gap or bubble, a combination of pneumatic and hydraulic pressure builds by compression of the air/gas and drug fluid and the force is relayed to the sliding pierceable seal.
  • the integrated sterile fluid pathway connection is connected (i.e., the fluid pathway is opened) by the combination pneumatic/hydraulic force of the air/gas and drug fluid within the drug chamber created by activation of a drive mechanism.
  • drug fluid is permitted to flow from the drug container, through the integrated sterile fluid pathway connection, sterile fluid conduit, and insertion mechanism, and into the body of the user for drug delivery.
  • the fluid flows through only a manifold and a cannula and/or needle of the insertion mechanism, thereby maintaining the sterility of the fluid pathway before and during drug delivery.
  • the drug pump is capable of delivering a range of drugs with different viscosities and volumes.
  • the drug pump is capable of delivering a drug at a controlled flow rate (speed) and/or of a specified volume.
  • the drug delivery process is controlled by one or more flow restrictors within the fluid pathway connection and/or the sterile fluid conduit.
  • other flow rates may be provided by varying the geometry of the fluid flow path or delivery conduit, varying the speed at which a component of the drive mechanism advances into the drug container to dispense the drug therein, or combinations thereof. Still further details about the fluid pathway connection 300 and the sterile fluid conduit 30 are provided hereinafter in later sections in reference to other embodiments.
  • a number of insertion mechanisms may be utilized within the drug pumps of embodiments of the present invention.
  • the pump-type delivery devices of embodiments of the present invention may be connected in fluid flow communication to a patient or user, for example, through any suitable hollow tubing.
  • a solid bore needle may be used to pierce the skin of the patient and place a hollow cannula at the appropriate delivery position, with the solid bore needle being removed or retracted prior to drug delivery to the patient.
  • the fluid can be introduced into the body through any number of means, including but not limited to: an automatically inserted needle, cannula, micro-needle array, or infusion set tubing.
  • a number of mechanisms may also be employed to activate the needle insertion into the patient.
  • a biasing member such as a spring may be employed to provide sufficient force to cause the needle and cannula to pierce the skin of the patient.
  • the same spring, an additional spring, or another similar mechanism may be utilized to retract the needle from the patient.
  • the insertion mechanism may generally be as described in International Patent Application No. PCT/US2012/53174 , which is included by reference herein in its entirety for all purposes.
  • Such a configuration may be utilized for insertion of the drug delivery pathway into, or below, the skin (or muscle) of the patient in a manner that minimizes pain to the patient.
  • Other known methods for insertion of a fluid pathway may be utilized and are contemplated within the bounds of embodiments of the present invention.
  • the insertion mechanism 200 includes an insertion mechanism housing having one or more lockout windows, and a base for connection to the assembly platform and/or pump housing (as shown in FIG. 1B and FIG. 1C ).
  • the connection of the base to the assembly platform 20 may be, for example, such that the bottom of the base is permitted to pass-through a hole in the assembly platform to permit direct contact of the base to the body of the user.
  • the bottom of the base may include a sealing membrane that is removable prior to use of the drug pump 10.
  • the insertion mechanism may further include one or more insertion biasing members, a needle, a retraction biasing member, a cannula, and a manifold.
  • the manifold may connect to sterile fluid conduit 30 to permit fluid flow through the manifold, cannula, and into the body of the user during drug delivery.
  • needle is intended to refer to a variety of needles including but not limited to conventional hollow needles, such as a rigid hollow steel needles, and solid core needles more commonly referred to as “trocars.”
  • the needle is a 27 gauge solid core trocar and in other embodiments, the needle may be any size needle suitable to insert the cannula for the type of drug and drug administration (e.g., subcutaneous, intramuscular, intradermal, etc.) intended.
  • a sterile boot may be utilized within the needle insertion mechanism.
  • the sterile boot is a collapsible sterile membrane that is in fixed engagement at a proximal end with the manifold and at a distal end with the base.
  • the sterile boot is maintained in fixed engagement at a distal end between base and insertion mechanism housing.
  • Base includes a base opening through which the needle and cannula may pass-through during operation of the insertion mechanism, as will be described further below. Sterility of the cannula and needle are maintained by their initial positioning within the sterile portions of the insertion mechanism. Specifically, as described above, needle and cannula are maintained in the sterile environment of the manifold and sterile boot.
  • the base opening of base may be closed from non-sterile environments as well, such as by for example a sealing membrane 254 (shown in FIG. 1C ).
  • the insertion mechanism is initially locked into a ready-to-use stage by lockout pin(s) which are initially positioned within lockout windows of the insertion mechanism housing.
  • lockout pin(s) which are initially positioned within lockout windows of the insertion mechanism housing.
  • insertion biasing member and retraction biasing member are each retained in their compressed, energized states.
  • the lockout pin(s) 208 may be directly displaced by user depression of the activation mechanism 14.
  • the activation mechanism 14 may be depressed to initiate the drug pump.
  • Depression of the activation mechanism 14 may directly cause translation or displacement of control arm 40 and directly or indirectly cause displacement of lockout pin(s) 208 from their initial position within locking windows 202A of insertion mechanism housing 202.
  • Displacement of the lockout pin(s) 208 permits insertion biasing member to decompress from its initial compressed, energized state. This decompression of the insertion biasing member drives the needle and the cannula into the body of the user.
  • the retraction biasing member is permitted to expand in the proximal direction from its initial energized state. This axial expansion in the proximal direction of the retraction biasing member retracts the needle, while maintaining the cannula in fluid communication with the body of the user.
  • the insertion mechanism may be used to insert a needle and cannula into the user and, subsequently, retract the needle while retaining the cannula in position for drug delivery to the body of the user.
  • drive mechanism 100 includes a drive housing 130, and a drug container 50 having a cap 52, a pierceable seal (not visible), a barrel 58, and a plunger seal 60.
  • the seals described herein may be comprised of a number of materials but are, in a preferred embodiment, comprised of one or more elastomers or rubbers.
  • the drive mechanism may further include a connection mount 54 to guide the insertion of the piercing member of the fluid pathway connection into the barrel 58 of the drug container 50.
  • the drive mechanism 100 may further contain one or more drive biasing members, one or more release mechanisms, and one or more guides, as are described further herein.
  • the components of the drive mechanism function to force a fluid from the drug container out through the pierceable seal, or preferably through the piercing member of the fluid pathway connection, for delivery through the fluid pathway connection, sterile fluid conduit, and insertion mechanism into the body of the user.
  • the drive mechanism 100 employs one or more compression springs as the biasing member(s).
  • the power and control system may be actuated to directly or indirectly release the compression spring(s) from an energized state.
  • the compression spring(s) may bear against and act upon the plunger seal to force the fluid drug out of the drug container.
  • the compression spring may bear against and act upon a piston which, in turn, acts upon the plunger seal to force the fluid drug out of the drug container.
  • the fluid pathway connection may be connected through the pierceable seal prior to, concurrently with, or after activation of the drive mechanism to permit fluid flow from the drug container, through the fluid pathway connection, sterile fluid conduit, and insertion mechanism, and into the body of the user for drug delivery.
  • the fluid flows through only a manifold and a cannula of the insertion mechanism, thereby maintaining the sterility of the fluid pathway before and during drug delivery.
  • the drive mechanism 100 includes a drug container 50 having a cap 52, a pierceable seal (not visible), a barrel 58, and a plunger seal 60, and optionally a connection mount 54.
  • the drug container 50 is mounted to a distal end of a drive housing 130.
  • a cover sleeve 140 may be utilized between the drive biasing member 122 and the interface surface 110C of the piston 110 to, for example, promote more even distribution of force from the drive biasing member 122 to the piston 110, prevent buckling of the drive biasing member 122, and/or hide biasing member from user view.
  • Interface surface 110C of piston 110 is caused to rest substantially adjacent to, or in contact with, a proximal end of seal 60.
  • the piston 110A, 110B may be comprised of two components and have an interface surface 110C to contact the plunger seal.
  • a tether, ribbon, string, or other retention strap (referred to herein as the "tether" 512) may be connected at one end to the piston 110A, 110B.
  • the tether 512 may be connected to the piston 110A, 110B by retention between the two components of the piston 110A, 110B when assembled.
  • the tether 512 is connected at another end to a winch drum 520 of a delivery control mechanism 500.
  • the delivery control mechanism 500 functions to control, meter, provide resistance, or otherwise prevent free axial translation of the piston 110A, 110B and plunger seal 60 utilized to force a drug substance out of a drug container 50. Accordingly, the delivery control mechanism 500 and the drive mechanism 100 (collectively referred to herein as the "controlled delivery drive mechanism") together function to control the rate or profile of drug delivery to the user.
  • the delivery control mechanisms 500 of embodiments of the present invention do not drive the delivery of fluid substances from the drug chamber 21.
  • the delivery of fluid substances from the drug chamber 21 is caused by the expansion of the biasing member 122 from its initial energized state acting upon the piston 110A, 110B and plunger seal 60.
  • the delivery control mechanisms 500 instead function to provide resistance to the free motion of the piston 110A, 110B and plunger seal 60 as they are pushed by the expansion of the biasing member 122 from its initial energized state.
  • the motor 530 is utilized only to control, meter, provide resistance, or otherwise prevent free axial translation of the plunger seal, instead of driving the translation of the plunger seal, a smaller and/or more energy efficient motor may be utilized by the novel embodiments of the present invention.
  • the delivery control mechanism 500 does not drive the delivery but only controls the delivery motion.
  • the tether limits or otherwise restrains the motion of the piston 110, 110B and plunger seal 60, but does not apply the force for the delivery.
  • the controlled delivery drive mechanisms and drug pumps of embodiments of the present invention include a motor 530 indirectly or directly connected to a tether metering the axial translation of the piston 110A, 110B and plunger seal 60, which are being driven to axially translate by the biasing member 122.
  • the motor 530 may, accordingly, be selected from a variety of electromechanical sources capable of incremental motion, such as brushed DC motors, EC motors, stepper motors, solenoids, or other technologies that can produce controlled motion. In at least one embodiment, the motor is most preferably a stepper motor.
  • the components of the drive mechanism 100 upon activation, may be used to drive axial translation in the distal direction of the plunger seal 60 of the drug container 50.
  • the drive mechanism 100 may include one or more compliance features which enable additional axial translation of the plunger seal 60 to, for example, ensure that substantially the entire drug dose has been delivered to the user.
  • the plunger seal 60 itself, may have some compressibility permitting a compliance push of drug fluid from the drug container.
  • the novel controlled delivery drive mechanisms of embodiments of the present invention may optionally integrate status indication into the drug dose delivery.
  • the status of the drive mechanism before, during, and after operation can be relayed to the power and control system to provide feedback to the user.
  • Such feedback may be tactile, visual, and/or auditory, as described above, and may be redundant such that more than one signal or type of feedback is provided to the user during use of the device.
  • the user may be provided an initial feedback to identify that the system is operational and ready for drug delivery.
  • the system may then provide one or more drug delivery status indications to the user.
  • the drive mechanism and drug pump may provide an end-of-dose indication. As the end-of-dose indication is tied to the piston reaching the end of its axial translation, the drive mechanism and drug pump provide a true end-of-dose indication to the user.
  • an end-of-dose status indication may be provided to the user once the status reader 544 contacts or recognizes the final status trigger 512A positioned on the tether 512 that would contact the status reader 544 at the end of axial travel of the piston 110A, 110B and plunger 60 within the barrel 58 of the drug container 50.
  • the tether 512 may have one or more status triggers 512A, such as electrical contacts, optical markings, or electromechanical pins or recesses, which are capable of contacting or being recognized by a status reader 544.
  • the status reader 544 may be, for example, an electrical switch reader to contact the corresponding electrical contacts, an optical reader to recognize the corresponding optical markings, or a mechanical or electromechanical reader configured to contact corresponding pins, holes, or similar aspects on the tether.
  • the status triggers 512A may be positioned along the tether 512 to be read or recognized at positions which correspond with the beginning and end of drug delivery, as well as at desired increments during drug delivery.
  • the rate or profile of drug delivery to the user is controlled by the motor 530, gear assembly, and winch drum 520 releasing the tether 512 and permitting expansion of the biasing member 122 and axial translation of the piston 110A, 110B and plunger seal 60.
  • the status triggers 512A of the tether 512 are contacted or recognized by the status reader 544 and the status of the drive mechanism before, during, and after operation can be relayed to the power and control system to provide feedback to the user.
  • the frequency of the incremental status indication may be varied as desired.
  • a range of status readers 544 may be utilized depending on the status triggers 512A utilized by the system.
  • the status reader 544 may apply a tensioning force to the tether 512.
  • the tether 512 goes slack and the status reader 544 is permitted to rotate about a fulcrum (shown in FIG.6 as a cylindrical protrusion from the side of the status reader 544). This rotation may operate an electrical or electromechanical switch, for example a switch within sensor 540, signaling slack in the tether 512 to the power and control system 400.
  • the status gear 528 may act as an encoder along with sensor 540.
  • the sensor/encoder combination is used to provide feedback of motor rotation, which in turn can be calibrated to the position of piston 110 when there is no slack in the tether 512.
  • the status reader 544 and sensor/encoder 540 provide positional feedback, end-of-dose signal, and error indication, such as an occlusion, by observing slack in the tether 512 prior to reaching the expected number of motor rotations as counted by the sensor/encoder 540.
  • FIG. 4A shows an isometric view of the drive mechanism, according to at least a first embodiment, during its initial locked stage.
  • a fluid such as a drug fluid
  • a fluid may be contained within barrel 58, in a drug chamber 21 between plunger seal 60 and pierceable seal (not visible), for delivery to a user.
  • the pierceable seal is adjacent or retained at least partially within cap 52.
  • a fluid pathway connection may be connected to the drug container through the pierceable seal 56.
  • this fluid connection may be facilitated by a piercing member of the fluid pathway connection which pierces the pierceable seal and completes the fluid pathway from the drug container, through the fluid pathway connection, the fluid conduit, the insertion mechanism, and the cannula for delivery of the drug fluid to the body of the user.
  • one or more locking mechanisms may retain the biasing member 122 in an initial energized position within piston 110A, 110B. Directly or indirectly upon activation of the device by the user, the locking mechanism may be removed to permit operation of the drive mechanism.
  • the piston 110 and biasing member 122 are both initially in a compressed, energized state behind the plunger seal 60.
  • biasing member 122 may be maintained in this state until activation of the device between internal features of drive housing 130 and interface surface 110C of piston 110A, 110B.
  • biasing member 122 is permitted to expand (i.e., decompress) axially in the distal direction (i.e., in the direction of the hatched arrow).
  • Such expansion causes the biasing member 122 to act upon and distally translate interface surface 110C and piston 110, thereby distally translating plunger seal 60 to push drug fluid out of the drug chamber 21 of barrel 58.
  • an end-of-dose status indication may be provided to the user once the status reader 544 contacts or recognizes a status trigger 512A positioned on the tether 512 to substantially correspond with the end of axial travel of the piston 110A, 110B and plunger seal 60 within the barrel 58 of the drug container 50.
  • the status triggers 512A are positioned along the tether 512 at various increments, such as increments which correspond to certain volume measurement, to provide incremental status indication to the user.
  • the status reader is an optical status reader configured to recognize the corresponding optical status triggers on the tether. As would be understood by an ordinarily skilled artisan, such optical status triggers may be markings which are recognizable by the optical status reader.
  • the status reader is a mechanical or electromechanical reader configured to physically contact corresponding pins, holes, or similar aspects on the tether. Electrical contacts could similarly be utilized on the tether as status indicators which contact or are otherwise recognized by the corresponding electrical status reader.
  • the status triggers 512A may be positioned along the tether 512 to be read or recognized at positions which correspond with the beginning and end of drug delivery, as well as at desired increments during drug delivery.
  • FIG. 5B shows a cross-sectional view of the view shown in FIG.
  • tether 512 passes substantially axially through the drive mechanism housing 130, the biasing member 122, and connects to the piston 110 A, 110B to restrict the axial translation of the piston 110A, 110B and the plunger seal 60 that resides adjacent thereto.
  • the delivery control mechanisms 500 of embodiments of the present invention do not drive the delivery of fluid substances from the drug chamber 21.
  • the delivery of fluid substances from the drug chamber 21 is caused by the expansion of the biasing member 122 from its initial energized state acting upon the piston 110A, 110B and plunger seal 60.
  • the delivery control mechanisms 500 instead function to provide resistance to the free motion of the piston 110A, 110B and plunger seal 60 as they are pushed by the expansion of the biasing member 122 from its initial energized state.
  • the biasing member 122 is permitted to continue its expansion from its energized state and drive the piston 110A, 110B and plunger seal 60 until the plunger seal 60 has substantially contacted the pierceable seal 56. This is visible in the cross-sectional view provided in FIG. 5C . At this point, substantially all of the drug substance has been pushed out of the drug chamber 21 through the fluid pathway connection 300 for drug delivery to the user.
  • a status trigger 512A may be configured along the tether 512 to correspond with this position of the piston 110A, 110B, such that, as the piston 110A, 110B reaches its end of axial travel, a status trigger 512A is read or recognized by the status reader 544 to provide true end-of-dose indication to the user.
  • the status triggers 512A may be positioned along the tether 512 to be read or recognized at positions which correspond with the beginning and end of drug delivery, as well as at desired increments during drug delivery.
  • the controlled delivery drive mechanisms and/or drug pumps of embodiments of the present invention may additionally enable a compliance push to ensure that substantially all of the drug substance has been pushed out of the drug chamber 21.
  • the plunger seal 60 itself, may have some compressibility permitting a compliance push of drug fluid from the drug container.
  • a pop-out plunger seal i.e., a plunger seal that is deformable from an initial state
  • the plunger seal may be caused to deform or "pop-out" to provide a compliance push of drug fluid from the drug container, as shown in FIG. 5C .
  • an electromechanical status switch and interconnect assembly may be utilized to contact, connect, or otherwise enable a transmission to the power and control system to signal end-of-dose to the user.
  • the status switch may be located distal to the pierceable seal 56 and the interconnect located proximal to the plunger seal 60 such that, upon substantially complete axial translation (and optional compliance push) of the plunger seal 60 within the barrel 58, the status switch and interconnect coordinate to enable a transmission to the power and control system to signal end-of-dose to the user.
  • This configuration further enables true end-of-dose indication to the user.
  • FIG. 6 shows a perspective view of certain components of a controlled delivery drive mechanism, according to at least one embodiment of the present invention.
  • the controlled delivery drive mechanism incorporates an incremental status indicator mechanism having a status reader and one or more corresponding status triggers.
  • the gear assembly of the delivery control mechanism 500 utilizes a motor 530 with pinion 530A.
  • the pinion 530A contacts a first gear 526A of a compound gear 526
  • the second gear 526B of the compound gear 526 contacts a gear aspect 524B of a worm gear 524.
  • the worm aspect 524A of the worm gear 524 contacts a drum gear 522 which is connected to a winch drum 520.
  • the tether 512 is at least partially wrapped around the winch drum 520.
  • a status reader 544 may read or recognize one or more corresponding status triggers 512A on the tether 512 to provide incremental status indication before, during, and after operation of the controlled delivery drive mechanism.
  • the drive mechanism shown in FIG. 6 may utilize a mechanical status reader 544 which is physically contacted by ridges, holes, or other aspects incrementally spaced on the tether 512 to correspond with desired status indications (e.g., volume delivered, volume remaining, changes in delivery rates or profiles, etc.).
  • desired status indications e.g., volume delivered, volume remaining, changes in delivery rates or profiles, etc.
  • the status reader 544 causes the sensor 540 to measure the position of the status gear 528 and transmit a signal to the power and control system for status indication to the user.
  • optical status readers and corresponding triggers, electromechanical status readers and corresponding triggers, and/or mechanical status readers and corresponding triggers may all be utilized by the embodiments of the present invention to provide incremental status indication to the user.
  • Assembly and/or manufacturing of controlled delivery drive mechanism 100, drug delivery pump 10, or any of the individual components may utilize a number of known materials and methodologies in the art.
  • a number of known cleaning fluids such as isopropyl alcohol and hexane may be used to clean the components and/or the devices.
  • a number of known adhesives or glues may similarly be employed in the manufacturing process.
  • known siliconization and/or lubrication fluids and processes may be employed during the manufacture of the novel components and devices.
  • known sterilization processes may be employed at one or more of the manufacturing or assembly stages to ensure the sterility of the final product.
  • the drive mechanism may be assembled in a number of methodologies.
  • the drug container 50 may first be assembled and filled with a fluid for delivery to the user.
  • the drug container 50 includes a cap 52, a pierceable seal 56, a barrel 58, and a plunger seal 60.
  • the pierceable seal 56 may be fixedly engaged between the cap 52 and the barrel 58, at a distal end of the barrel 58.
  • the barrel 58 may be filled with a drug fluid through the open proximal end prior to insertion of the plunger seal 60 from the proximal end of the barrel 58.
  • An optional connection mount 54 may be mounted to a distal end of the pierceable seal 56.
  • the connection mount 54 may guide the insertion of the piercing member of the fluid pathway connection into the barrel 58 of the drug container 50.
  • the drug container 50 may then be mounted to a distal end of drive housing 130.
  • a drive biasing member 122 may be inserted into a distal end of the drive housing 130.
  • a cover sleeve 140 may be inserted into a distal end of the drive housing 130 to substantially cover biasing member 122.
  • a piston may be inserted into the distal end of the drive housing 130 such that it resides at least partially within an axial pass-through of the biasing member 122 and the biasing member 122 is permitted to contact a piston interface surface 110C of piston 110A, 110B at the distal end of the biasing member 122.
  • An optional cover sleeve 140 may be utilized to enclose the biasing member 122 and contact the piston interface surface 110C of piston 110A, 110B.
  • the piston 110A, 110B and drive biasing member 122, and optional cover sleeve 140 may be compressed into drive housing 130.
  • Such assembly positions the drive biasing member 122 in an initial compressed, energized state and preferably places a piston interface surface 110C in contact with the proximal surface of the plunger seal 60 within the proximal end of barrel 58.
  • the piston, piston biasing member, contact sleeve, and optional components may be compressed and locked into the ready-to-actuate state within the drive housing 130 prior to attachment or mounting of the drug container 50.
  • the tether 512 is pre-connected to the proximal end of the piston 110A, 110B and passed through the axial aperture of the biasing member 122 and drive mechanism 130, and then wound through the interior of the drug pump with the other end of the tether 512 wrapped around the winch drum 520 of the delivery control mechanism 500.
  • a fluid pathway connection and specifically a sterile sleeve of the fluid pathway connection, may be connected to the cap and/or pierceable seal of the drug container.
  • a fluid conduit may be connected to the other end of the fluid pathway connection which itself is connected to the insertion mechanism such that the fluid pathway, when opened, connected, or otherwise enabled travels directly from the drug container, fluid pathway connection, fluid conduit, insertion mechanism, and through the cannula for drug delivery into the body of a user.
  • the components which constitute the pathway for fluid flow are now assembled. These components may be sterilized, by a number of known methods, and then mounted either fixedly or removably to an assembly platform or housing of the drug pump, as shown in FIG. 1B .
  • the embodiments may include one or more batteries utilized to power the motor, drive mechanisms, and drug pumps of embodiments of the present invention. A range of batteries known in the art may be utilized for this purpose.
  • upper or lower housings may optionally contain one or more transparent or translucent windows 18, as shown in FIG. 1A , to enable the user to view the operation of the drug pump 10 or verify that drug dose has completed.
  • the drug pump 10 may contain an adhesive patch 26 and a patch liner 28 on the bottom surface of the housing 12. The adhesive patch 26 may be utilized to adhere the drug pump 10 to the body of the user for delivery of the drug dose.
  • the adhesive patch 26 may have an adhesive surface for adhesion of the drug pump to the body of the user.
  • the adhesive surface of the adhesive patch 26 may initially be covered by a non-adhesive patch liner 28, which is removed from the adhesive patch 26 prior to placement of the drug pump 10 in contact with the body of the user. Removal of the patch liner 28 may further remove the sealing membrane 254 of the insertion mechanism 200, opening the insertion mechanism to the body of the user for drug delivery (as shown in FIG. 1C ).
  • controlled delivery drive mechanism 100 and drug pump 10 may be modified.
  • the housing of drug pump 10 is shown as two separate components upper housing 12A and lower housing 12B, these components may be a single unified component.
  • a glue, adhesive, or other known materials or methods may be utilized to affix one or more components of the controlled delivery drive mechanism and/or drug pump to each other.
  • one or more components of the controlled delivery drive mechanism and/or drug pump may be a unified component.
  • the upper housing and lower housing may be separate components affixed together by a glue or adhesive, a screw fit connection, an interference fit, fusion joining, welding, ultrasonic welding, and the like; or the upper housing and lower housing may be a single unified component.
  • a glue or adhesive e.g., glue or adhesive
  • a screw fit connection e.g., a screw fit connection
  • an interference fit e.g., an interference fit
  • fusion joining e.g., welding, ultrasonic welding, and the like
  • welding ultrasonic welding
  • the upper housing and lower housing may be a single unified component.
  • the controlled delivery drive mechanisms and drug pumps disclosed herein provide an efficient and easily-operated system for automated drug delivery from a drug container.
  • the novel embodiments described herein provide drive mechanisms for the controlled delivery of drug substances and drug delivery pumps which incorporate such controlled delivery drive mechanisms.
  • the drive mechanisms of embodiments of the present invention control the rate of drug delivery by metering, providing resistance, or otherwise preventing free axial translation of the plunger seal utilized to force a drug substance out of a drug container and, thus, are capable of delivering drug substances at variable rates and/or delivery profiles.
  • the drive mechanisms of embodiments of the present invention provide integrated status indication features which provide feedback to the user before, during, and after drug delivery.
  • the user may be provided an initial feedback to identify that the system is operational and ready for drug delivery. Upon activation, the system may then provide one or more drug delivery status indications to the user. At completion of drug delivery, the drive mechanism and drug pump may provide an end-of-dose indication.
  • the novel controlled delivery drive mechanisms of embodiments of the present invention may be directly or indirectly activated by the user. Furthermore, the novel configurations of the controlled delivery drive mechanism and drug pumps of embodiments of the present invention maintain the sterility of the fluid pathway during storage, transportation, and through operation of the device. Because the path that the drug fluid travels within the device is entirely maintained in a sterile condition, only these components need be sterilized during the manufacturing process.
  • Such components include the drug container of the drive mechanism, the fluid pathway connection, the sterile fluid conduit, and the insertion mechanism.
  • the power and control system, the assembly platform, the control arm, the activation mechanism, the housing, and other components of the drug pump do not need to be sterilized. This greatly improves the manufacturability of the device and reduces associated assembly costs. Accordingly, the devices of the present invention do not require terminal sterilization upon completion of assembly.
  • Manufacturing of a drug pump includes the step of attaching both the controlled delivery drive mechanism and drug container, either separately or as a combined component, to an assembly platform or housing of the drug pump.
  • the method of manufacturing further includes attachment of the fluid pathway connection, drug container, and insertion mechanism to the assembly platform or housing.
  • the additional components of the drug pump, as described above, including the power and control system, the activation mechanism, and the control arm may be attached, preformed, or pre-assembled to the assembly platform or housing.
  • An adhesive patch and patch liner may be attached to the housing surface of the drug pump that contacts the user during operation of the device.
  • a method of operating the drug pump includes the steps of: activating, by a user, the activation mechanism; displacing a control arm to actuate an insertion mechanism; and actuating a power and control system to activate a controlled delivery drive mechanism to drive fluid drug flow through the drug pump according to a controlled rate or drug delivery profile.
  • the method may further include the step of: engaging an optional on-body sensor prior to activating the activation mechanism.
  • the method similarly may include the step of: establishing a connection between a fluid pathway connection to a drug container.
  • the method of operation may include translating a plunger seal within the controlled delivery drive mechanism by the expansion of the biasing member acting upon a piston within a drug container to force fluid drug flow through the drug container, the fluid pathway connection, a sterile fluid conduit, and the insertion mechanism for delivery of the fluid drug to the body of a user, wherein a tether is utilized to restrain the free axial translation of the piston.
  • the method of operation of the insertion mechanism and the drug pump may be better appreciated with reference to FIGS. 4A-4C and FIGS. 5A-5C , as described above.

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  • Health & Medical Sciences (AREA)
  • Vascular Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)
  • Reciprocating Pumps (AREA)

Claims (23)

  1. Mécanisme d'entraînement d'administration commandée (100) pour un conteneur de médicaments présentant un joint de piston (60) configuré pour se déplacer au sein d'un fût (58), le mécanisme d'entraînement d'administration commandée (100) comprenant : un carter d'entraînement (130) ; un piston (110A, 110B) ; un élément d'actionnement (122), dans lequel l'élément d'actionnement (122) est initialement maintenu dans un état alimenté en énergie et est configuré pour appuyer sur une surface d'interface (110C) du piston (110) ; un câble d'attache (512) raccordé, au niveau d'une extrémité, au piston (110A, 110B) et, au niveau d'une autre extrémité, à un tambour de cabestan (520) d'un mécanisme de commande d'administration (500), dans lequel une force de mise en tension est appliquée au câble d'attache (512) afin de limiter la liberté d'expansion de l'élément d'actionnement (122) à partir de son état initial alimenté en énergie et la liberté de déplacement axial du piston (110A, 110B) sur lequel appuie l'élément d'actionnement (122) ; caractérisé en ce qu'un dispositif de lecture de statut (544) est agencé adjacent au câble d'attache (512), le dispositif de lecture de statut (544) étant configuré pour fournir un signal lorsqu'un relâchement se produit dans le câble d'attache (512).
  2. Mécanisme d'entraînement (100) selon la revendication 1, dans lequel le dispositif de lecture de statut (544) applique une force de mise en tension au câble d'attache (512).
  3. Mécanisme d'entraînement (100) selon la revendication 1 ou 2, dans lequel le dispositif de lecture de statut (544) peut tourner autour d'un point de pivot lorsque le câble d'attache (512) se relâche.
  4. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 4, dans lequel le dispositif de lecture de statut (544) comprend un commutateur.
  5. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 4, dans lequel le conteneur de médicament (50) contient un fluide médicamenteux au sein d'un compartiment à médicament (21).
  6. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 5, dans lequel un manchon de protection (140) peut être utilisé entre l'élément d'actionnement (122) et la surface d'interface (110C) du piston (110A, 110B).
  7. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 6, dans lequel le câble d'attache (512) est configuré pour être libéré à partir d'un tambour de cabestan (520) du mécanisme de commande d'administration (500) afin de mesurer la liberté d'expansion de l'élément d'actionnement (122) à partir de son état initial alimenté en énergie et la liberté de translation axiale du piston (110A, 110B) sur lequel appuie l'élément d'actionnement (122).
  8. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 7, comprenant en outre un ensemble d'engrenages présentant une pluralité d'engrenages, dans lequel au moins un desdits engrenages (528) est configuré pour faire office de dispositif d'encodage.
  9. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 8, comprenant un ensemble d'engrenages présentant un engrenage de cabestan (522) raccordé à un tambour de cabestan (520) sur lequel le câble d'attache (512) peut être enroulé de manière libérable, une vis sans fin (524) raccordée par mise en prise à l'engrenage de cabestan (522), un engrenage composé (526) raccordé par mise en prise à la vis sans fin (524), et un moteur (530) présentant un pignon (530A) raccordé par mise en prise à l'engrenage composé 526, dans lequel le moteur (530) est configuré pour entraîner l'ensemble d'engrenages afin de libérer le câble d'attache (512) par rapport au tambour de cabestan (520) afin de réguler la liberté d'expansion de l'élément d'actionnement (122) à partir de son état initial alimenté en énergie et la liberté de translation axiale du piston (110A, 110B) sur lequel appuie l'élément d'actionnement (122).
  10. Mécanisme d'entraînement (100) selon la revendication 7, dans lequel la régulation du câble d'attache (512) grâce au moteur (530) commande la vitesse ou le profil d'administration de médicament à un utilisateur.
  11. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 10, dans lequel le piston (110A, 110B) est constitué d'une ou plusieurs partie(s) et se raccorde à une extrémité distale du câble d'attache (512).
  12. Mécanisme d'entraînement (100) selon l'une quelconque des revendications 1 à 11, dans lequel le dispositif de lecture de statut (544) peut être configuré pour lire ou reconnaître un ou plusieurs élément(s) déclencheur(s) de statut (512A) correspondant(s) espacé(s) de manière incrémentielle sur le câble d'attache (512), dans lequel, pendant le fonctionnement du mécanisme d'entraînement (100), une interaction entre le dispositif de lecture de statut (544) et les éléments déclencheurs de statut (512A) émet un signal vers un système d'alimentation et de commande (400) afin de fournir une rétroaction à un utilisateur.
  13. Mécanisme d'entraînement (100) selon la revendication 12, dans lequel le dispositif de lecture de statut (544) est un dispositif de lecture de statut optique et les éléments déclencheurs de statut (512A) correspondants sont des éléments déclencheurs de statut optiques.
  14. Mécanisme d'entraînement (100) selon la revendication 12, dans lequel le dispositif de lecture de statut (544) est un dispositif de lecture de statut électromécanique et les éléments déclencheurs de statut (512A) correspondants sont des éléments déclencheurs de statut électromécaniques.
  15. Mécanisme d'entraînement (100) selon la revendication 12, dans lequel le dispositif de lecture de statut (544) est un dispositif de lecture de statut mécanique et les éléments déclencheurs de statut (512A) correspondants sont des éléments déclencheurs de statut mécaniques.
  16. Pompe d'administration de médicament (10) avec administration de médicament commandée, qui comprend un carter (12) et une plateforme d'assemblage (20), sur laquelle se trouve un mécanisme d'activation (14), un mécanisme d'insertion (200), un raccord de passage de fluide (300), un système d'alimentation et de commande (400), et un mécanisme d'entraînement d'administration commandée (100) selon l'une quelconque des revendications 1 à 15.
  17. Pompe d'administration de médicament (10) selon la revendication 16, dans laquelle le système d'alimentation et de commande (400) est configuré pour recevoir une ou plusieurs entrée(s) afin de réguler la libération du câble d'attache (512) grâce au tambour de cabestan (520) et permettre ainsi une translation axiale du piston (110) grâce à l'élément d'actionnement (122) afin de déplacer un joint de piston (60) au sein d'un fût (58).
  18. Pompe d'administration de médicament (10) selon la revendication 16 ou 17, dans laquelle la ou les entrée(s) sont fournie(s) par l'utilisateur agissant sur le mécanisme d'activation (14).
  19. Pompe d'administration de médicament (10) selon la revendication 16 ou 17, dans laquelle la ou les entrée(s) sont fournie(s) par l'utilisateur agissant sur une interface de commande.
  20. Pompe d'administration de médicament (10) selon la revendication 16 ou 17, dans laquelle la ou les entrée(s) sont fournie(s) par l'utilisateur en agissant sur un mécanisme de commande à distance.
  21. Pompe d'administration de médicament (10) selon l'une quelconque des revendications 16 à 20, dans laquelle le système d'alimentation et de commande (400) est configuré pour recevoir une ou plusieurs entrée(s) afin d'ajuster la limitation, fournie par le câble d'attache (512) et le tambour de cabestan (520), de la liberté de translation axiale du piston (110A, 110B) sur lequel appuie l'élément d'actionnement (122) afin de parvenir à une vitesse ou un profil souhaité(e) d'administration de médicament.
  22. Pompe d'administration de médicament (10) selon l'une quelconque des revendications 16 à 20, dans laquelle le système d'alimentation et de commande (400) est configuré pour recevoir une ou plusieurs entrée(s) afin d'ajuster la limitation, fournie par le câble d'attache (512) et le tambour de cabestan (520), de la liberté de translation axiale du piston (110A, 110B) sur lequel appuie l'élément d'actionnement (122) afin de modifier le volume de dose pour une administration à l'utilisateur.
  23. Pompe d'administration de médicament (10) selon l'une quelconque des revendications 16 à 20, dans laquelle le système d'alimentation et de commande (400) est configuré pour recevoir une ou plusieurs entrée(s) afin d'ajuster la limitation, fournie par le câble d'attache (512) et le tambour de cabestan (520), de la liberté de translation axiale du piston (110A, 110B) sur lequel appuie l'élément d'actionnement (122) afin de démarrer, arrêter, ou mettre en pause le fonctionnement du mécanisme d'entraînement (100).
EP13762335.1A 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament Not-in-force EP2890431B1 (fr)

Priority Applications (3)

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EP17162587.4A EP3225265A1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
EP16151332.0A EP3028727B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
DK16151332.0T DK3028727T3 (en) 2012-08-29 2013-08-29 CONTROLLED DELIVERY DRIVE MECHANISM FOR MEDICAL DELIVERY PUMP

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US201261694534P 2012-08-29 2012-08-29
US201261731744P 2012-11-30 2012-11-30
US201361748667P 2013-01-03 2013-01-03
PCT/US2013/057259 WO2014036239A2 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament

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EP16151332.0A Division-Into EP3028727B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
EP16151332.0A Division EP3028727B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament

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EP2890431A2 EP2890431A2 (fr) 2015-07-08
EP2890431B1 true EP2890431B1 (fr) 2016-12-21

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EP16151332.0A Not-in-force EP3028727B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
EP13763364.0A Active EP2890433B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
EP13762339.3A Not-in-force EP2890432B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée à vitesse variable pour pompes d'administration de médicament
EP13762335.1A Not-in-force EP2890431B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
EP17163810.9A Active EP3210636B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée à vitesse variable pour pompes d'administration de médicament
EP17162587.4A Withdrawn EP3225265A1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament

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EP13763364.0A Active EP2890433B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament
EP13762339.3A Not-in-force EP2890432B1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée à vitesse variable pour pompes d'administration de médicament

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EP17162587.4A Withdrawn EP3225265A1 (fr) 2012-08-29 2013-08-29 Mécanismes d'entraînement d'administration commandée pour pompes d'administration de médicament

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US (5) US10251996B2 (fr)
EP (6) EP3028727B1 (fr)
JP (5) JP6645829B2 (fr)
KR (3) KR20150048832A (fr)
CN (3) CN104582755B (fr)
AU (3) AU2013308678B2 (fr)
BR (2) BR112015003694A2 (fr)
CA (3) CA2881305C (fr)
DK (4) DK3028727T3 (fr)
ES (3) ES2639096T3 (fr)
HK (2) HK1211885A1 (fr)
IL (3) IL236958B (fr)
MX (4) MX354141B (fr)
PT (4) PT2890433T (fr)
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Families Citing this family (90)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE602005023458D1 (de) 2005-09-12 2010-10-21 Unomedical As Einfürungssystem für ein Infusionsset mit einem ersten und zweiten Federeinheit
WO2011121023A1 (fr) 2010-03-30 2011-10-06 Unomedical A/S Dispositif médical
US10194938B2 (en) 2011-03-14 2019-02-05 UnoMedical, AS Inserter system with transport protection
CA2845367C (fr) 2011-09-02 2019-09-17 Unitract Syringe Pty Ltd Mecanisme d'entrainement pour des pompes d'administration de medicaments a indication integree de l'etat
US9814832B2 (en) 2011-09-02 2017-11-14 Unl Holdings Llc Drive mechanism for drug delivery pumps with integrated status indication
US9707335B2 (en) 2011-09-02 2017-07-18 Unitract Syringe Pty Ltd Drive mechanism for drug delivery pumps with integrated status indication
US11173244B2 (en) 2011-09-02 2021-11-16 Unl Holdings Llc Drive mechanism for drug delivery pumps with integrated status indication
US11197689B2 (en) 2011-10-05 2021-12-14 Unomedical A/S Inserter for simultaneous insertion of multiple transcutaneous parts
EP2583715A1 (fr) 2011-10-19 2013-04-24 Unomedical A/S Système de tube de perfusion et procédé de fabrication
BR112015003694A2 (pt) 2012-08-29 2017-07-04 Unitract Syringe Pty Ltd mecanismo de acionamento de entrega controlada e bomba de entrega de fármaco com entrega de fármaco controlada
CA2896708A1 (fr) 2012-12-27 2014-07-03 Kaleo, Inc. Dispositifs, systemes et procedes de localisation et d'interaction avec des systemes d'administration de medicament
DE202013000411U1 (de) * 2013-01-16 2013-01-24 H & B Electronic Gmbh & Co. Kg Dauerinfusionsvorrichtung
DK2948205T3 (en) * 2013-01-25 2018-02-05 Unl Holdings Llc DRIVE MECHANISM FOR PHARMACEUTICAL DISPENSER PUMPS WITH INTEGRATED STATUS INDICATOR
US9591740B2 (en) 2013-03-08 2017-03-07 Tri Alpha Energy, Inc. Negative ion-based neutral beam injector
EP3021899A1 (fr) * 2013-07-17 2016-05-25 Sanofi Configuration d'entraînement pour un dispositif d'administration de médicaments
GB2516896B (en) * 2013-08-05 2020-08-12 Owen Mumford Ltd Injection devices
TWI569832B (zh) * 2013-10-23 2017-02-11 卡貝歐洲有限公司 藥物輸送裝置
WO2015102987A1 (fr) * 2013-12-31 2015-07-09 Biogen Ma Inc. Moteur de pompe à perfusion avec ressort de compression
WO2015117131A1 (fr) * 2014-02-03 2015-08-06 Unitract Syringe Pty Ltd Tiges de piston extensibles pour seringues
CN106456883B (zh) * 2014-03-12 2019-11-05 魏民 自动药物注射装置
KR102416904B1 (ko) * 2014-06-03 2022-07-04 암겐 인코포레이티드 약물 전달 디바이스에 의해 수집된 데이터를 원격으로 프로세싱하기 위한 시스템들 및 방법들
TWI689326B (zh) * 2014-08-06 2020-04-01 加拿大商複製細胞生命科學公司 注射裝置
WO2016049501A1 (fr) 2014-09-26 2016-03-31 Unitract Syringe Pty Ltd Récipients de médicament à tube concentrique et pompes d'administration de médicament permettant le mélange et l'administration
CN106999655B (zh) * 2014-12-08 2021-04-06 赛诺菲 用于组装药物输送装置的方法和药物输送装置
EP3229864A1 (fr) * 2014-12-08 2017-10-18 Sanofi Dispositif d'administration de médicament avec mécanisme d'entraînement
GB2534599A (en) * 2015-01-29 2016-08-03 Owen Mumford Ltd A medicament delivery device
CA2978017A1 (fr) 2015-03-02 2016-09-09 Amgen Inc. Dispositif et procede d'obtention de raccords aseptiques
EA036104B1 (ru) * 2015-03-09 2020-09-29 Эмджен Инк. Приводные механизмы для помп подачи лекарства
CA2979044C (fr) 2015-03-10 2022-10-18 Regeneron Pharmaceuticals, Inc. Procede et systeme de percage aseptique
CN104815369B (zh) * 2015-04-30 2017-09-05 于振燕 Icu科微量注射泵装置
US11357923B2 (en) * 2015-10-13 2022-06-14 Eli Lilly And Company Zero position sensing system for medication delivery device
CN105194757B (zh) * 2015-10-27 2018-04-03 李绪祯 全自动便携式输液泵及其使用方法
US10449306B2 (en) * 2015-11-25 2019-10-22 Medtronics Minimed, Inc. Systems for fluid delivery with wicking membrane
US10406282B2 (en) * 2015-12-10 2019-09-10 Repro-Med Systems, Inc. System and method for a syringe micro pump with volute spring
US11357912B2 (en) 2016-01-19 2022-06-14 Unomedical A/S Cannula and infusion devices
JOP20170042B1 (ar) 2016-02-12 2022-09-15 Amgen Inc وسيلة توصيل عقار، طريقة تصنيعه وطريقة استخدامه
CN108697846B (zh) * 2016-02-19 2021-09-10 伟创力有限责任公司 具有磁驱动系统的自动注射装置
US10967118B2 (en) 2016-02-19 2021-04-06 Flex, Ltd. Automatic injection device having a magnetic drive system
WO2017159779A1 (fr) 2016-03-16 2017-09-21 コスメディ製薬株式会社 Boîtier de timbre à micro-aiguilles
EP3439715B1 (fr) * 2016-04-08 2021-03-10 Amgen Inc. Dispositif d'administration de médicament
EP3445421A4 (fr) 2016-04-18 2020-01-01 Medtrum Technologies Inc. Mécanisme d'entraînement unilatéral pour système de perfusion portatif
US10549044B2 (en) 2016-06-09 2020-02-04 Becton, Dickinson And Company Spacer assembly for drug delivery system
CN106110434A (zh) * 2016-06-22 2016-11-16 重庆科技学院 流量可调机械自动输液仪
WO2018005915A1 (fr) 2016-06-30 2018-01-04 West Pharmaceutical Services, Inc. Dispositif d'entraînement de seringue, commandé par un patient, réutilisable
KR101710887B1 (ko) * 2016-07-04 2017-03-13 박라미 화장품 흡수를 위한 피부 자극기
EP3496784A4 (fr) 2016-08-08 2020-01-22 UNL Holdings LLC Dispositif d'administration de médicament et méthode pour connecter une voie d'écoulement de fluide
KR101923267B1 (ko) * 2016-08-12 2018-11-28 주식회사 동방메디컬 약물 카트리지 및 이를 구비하는 약물주입기
US10695487B2 (en) 2016-08-30 2020-06-30 Unl Holdings Llc Controlled delivery drive mechanisms for drug delivery pumps
WO2018136194A1 (fr) 2017-01-17 2018-07-26 West Pharma. Services IL, Ltd. Injecteur actionné par ressort incurvé
US10332623B2 (en) 2017-01-17 2019-06-25 Kaleo, Inc. Medicament delivery devices with wireless connectivity and event detection
WO2018136717A1 (fr) * 2017-01-20 2018-07-26 Biogen Ma Inc. Injecteur intelligent
CN110559508B (zh) * 2017-03-30 2021-06-01 南京溧水高新产业股权投资有限公司 一种输液瓶自动更换装置
EP3862038A1 (fr) * 2017-03-31 2021-08-11 Becton, Dickinson and Company Dispositif d'injection et/ou de perfusion portable intelligent
FR3065646B1 (fr) * 2017-04-26 2019-06-14 Aptar France Sas Dispositif d'injection automatique de produit fluide
EP3618895B1 (fr) * 2017-05-05 2022-04-13 Regeneron Pharmaceuticals, Inc. Auto-injecteur
KR102239217B1 (ko) * 2017-07-11 2021-04-12 한양대학교 산학협력단 흡인 압력이 일정한 의료용 흡인기
CA3069538A1 (fr) * 2017-07-19 2019-01-24 Smiths Medical Asd, Inc. Agencements de boitier pour pompes a perfusion
US11590279B2 (en) * 2017-07-20 2023-02-28 Flex Ltd. Clock mechanism flow regulator
KR101999364B1 (ko) * 2017-07-21 2019-07-12 서울대학교병원 기계식 자동 약물 투여 장치
US11617837B2 (en) 2017-07-25 2023-04-04 Amgen Inc. Drug delivery device with gear module and related method of assembly
CA3074354A1 (fr) * 2017-08-30 2019-03-07 Unl Holdings Llc Mecanismes d'entrainement d'administration commandee pour pompes d'administration de medicament
JP7086976B2 (ja) * 2017-09-29 2022-06-20 テルモ株式会社 プランジャ組立体、薬液投与装置及びプランジャ組立体の駆動方法
US11464903B2 (en) 2017-10-09 2022-10-11 Amgen Inc. Drug delivery device with drive assembly and related method of assembly
US10994116B2 (en) * 2018-06-30 2021-05-04 Bioq Pharma Incorporated Drug cartridge-based infusion pump
US11929160B2 (en) 2018-07-16 2024-03-12 Kaleo, Inc. Medicament delivery devices with wireless connectivity and compliance detection
DE102018118630A1 (de) 2018-08-01 2020-02-06 B. Braun Melsungen Ag Infusionssystem mit Infusionspumpe und damit kuppelbaren Pumpmodul
CN110354338B (zh) * 2018-09-03 2024-04-26 上海北昂医药科技股份有限公司 具有旋转分配及注射功能的泵阀一体装置
FR3086176B1 (fr) * 2018-09-20 2022-11-04 Aptar France Sas Autoinjecteur.
EP3972672A4 (fr) 2019-05-20 2023-06-21 Unomedical A/S Dispositif de perfusion rotative et méthodes associées
US20200384184A1 (en) * 2019-06-06 2020-12-10 Orlando Health, Inc. Wound irrigation device
CA3091601A1 (fr) * 2019-09-18 2021-03-18 Heraeus Medical Gmbh Dispositif d`application locale temporaire de fluides
GB2587804A (en) * 2019-09-27 2021-04-14 West Pharmaceutical Services Il Ltd Multi-rate drug delivery device and method of controlling the device
BR112022005788A2 (pt) 2019-10-01 2022-06-21 Unomedical As Conector
JP6937396B2 (ja) * 2020-01-31 2021-09-22 セイコーインスツル株式会社 定量送り機構及び吐出装置
JP6937397B2 (ja) * 2020-01-31 2021-09-22 セイコーインスツル株式会社 薬液ポンプ及び薬液投与装置
JP7396920B2 (ja) * 2020-02-12 2023-12-12 テルモ株式会社 薬液投与装置
JP7411435B2 (ja) * 2020-02-12 2024-01-11 テルモ株式会社 薬液投与装置
CN111282088B (zh) * 2020-03-01 2021-09-03 杭州丽脂医疗科技有限公司和兴路医疗美容门诊部 精准可微调定量的自体脂肪填充装置
US11980739B2 (en) 2020-08-18 2024-05-14 Becton, Dickinson And Company Double-acting, telescoping screw-driven pump mechanism disposed externally to reservoir in fluid delivery device
US11120824B1 (en) 2020-08-26 2021-09-14 Seagate Technology Llc Bolometric sensor for a heat-assisted magnetic recording device
CN216571055U (zh) * 2020-08-31 2022-05-24 贝克顿·迪金森公司 一种旋转计量泵
KR102308887B1 (ko) * 2020-09-16 2021-10-05 부경대학교 산학협력단 무전력 유체 펌프
WO2022090981A1 (fr) * 2020-10-28 2022-05-05 Patel Karna Nikhil Dispositif d'injection de fluide dans un corps
CN112169068A (zh) * 2020-11-02 2021-01-05 张超 一种心脏供血治疗器
US20220288304A1 (en) * 2021-03-12 2022-09-15 Insulet Corporation Drive mechanisms for positive displacement pumps
USD1007676S1 (en) 2021-11-16 2023-12-12 Regeneron Pharmaceuticals, Inc. Wearable autoinjector
EP4458384A1 (fr) * 2022-01-04 2024-11-06 Eoflow Co., Ltd. Dispositif d'injection de solution médicamenteuse
WO2023132493A1 (fr) * 2022-01-04 2023-07-13 이오플로우㈜ Ensemble réservoir et dispositif d'injection de médicament liquide le comprenant
KR20240010112A (ko) * 2022-07-15 2024-01-23 서울대학교산학협력단 자동 투약 기능을 가지는 이식형 디바이스
WO2024073398A1 (fr) * 2022-09-30 2024-04-04 Insulet Corporation Actionneur à double roue

Family Cites Families (208)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1929774A (en) * 1929-01-10 1933-10-10 Alemite Corp Lubricating apparatus
US3413974A (en) 1963-06-26 1968-12-03 Milton J. Cohen Hypodermic syringes
US3336924A (en) 1964-02-20 1967-08-22 Sarnoff Two compartment syringe package
US3401692A (en) 1964-06-26 1968-09-17 Micro Tek Instr Corp Syringe provided with a lateral vent and having high compression seals within the syringe bore
US3631847A (en) * 1966-03-04 1972-01-04 James C Hobbs Method and apparatus for injecting fluid into the vascular system
US3701345A (en) * 1970-09-29 1972-10-31 Medrad Inc Angiographic injector equipment
US3886938A (en) * 1973-10-23 1975-06-03 Scala Anthony Power operated fluid infusion device
US3940003A (en) 1974-05-07 1976-02-24 Pharmaco, Inc. Safety cap for medicament vial having puncturable seal
US4004586A (en) 1975-03-12 1977-01-25 Baxter Travenol Laboratories, Inc. Method and apparatus for sealed, sterile connection
US4048997A (en) 1976-11-01 1977-09-20 Mpl, Inc. Syringe with actinic radiation protection
US4313439A (en) 1980-03-24 1982-02-02 Biotek, Inc. Automated, spring-powered medicament infusion system
DE3367854D1 (en) 1982-10-27 1987-01-15 Duphar Int Res Automatic injection device
US4685903A (en) 1984-01-06 1987-08-11 Pacesetter Infusion, Ltd. External infusion pump apparatus
US4602700A (en) 1984-06-15 1986-07-29 Daltex Medical Sciences, Inc. Fail-safe mechanical drive for syringe
US4676122A (en) * 1984-06-15 1987-06-30 Daltex Medical Sciences, Inc. Fail-safe mechanical drive for syringe
DE3439322C2 (de) * 1984-10-26 1987-01-08 Infors GmbH, 8000 München Infusionspumpe
EP0204977A1 (fr) * 1985-05-14 1986-12-17 Ivion Corporation Appareil pour la commande de seringues
JPH0236519Y2 (fr) * 1985-10-25 1990-10-04
US4673400A (en) 1986-02-10 1987-06-16 Martin Ivan W Aseptic connector assembly for conduits for sterile fluids
US4755173A (en) 1986-02-25 1988-07-05 Pacesetter Infusion, Ltd. Soft cannula subcutaneous injection set
JPH072182B2 (ja) 1986-04-07 1995-01-18 テルモ株式会社 輸液ポンプ
JPH0515956Y2 (fr) 1987-05-27 1993-04-27
US4755172A (en) 1987-06-30 1988-07-05 Baldwin Brian E Syringe holder/driver and syringe arrangement and syringe/holder driver therefor
ATA228987A (de) 1987-09-09 1993-07-15 Pickhard Ewald Injektionsvorrichtung mit einer verformbaren ampulle
US4921487A (en) 1988-09-21 1990-05-01 Compagnie Financiere Saint. Nicolas External device for injecting medicine
USD326611S (en) 1988-12-09 1992-06-02 Euroitalia S.R.L. Bottle
US5167816A (en) 1990-08-20 1992-12-01 Abbott Laboratories Sterile coupling device for drug container
US5254096A (en) 1992-09-23 1993-10-19 Becton, Dickinson And Company Syringe pump with graphical display or error conditions
GB2271391B (en) * 1992-10-12 1995-08-02 Hornche Trading Co Ltd Automatic grease dispenser
DE4310808C2 (de) 1993-04-02 1995-06-22 Boehringer Mannheim Gmbh System zur Dosierung von Flüssigkeiten
FR2715071B1 (fr) 1994-01-17 1996-03-01 Aguettant Lab Injecteur automatique de médicament.
US5637095A (en) * 1995-01-13 1997-06-10 Minimed Inc. Medication infusion pump with flexible drive plunger
US5795339A (en) 1995-03-07 1998-08-18 Becton Dickinson And Company Catheter-advancement actuated needle retraction system
US5807334A (en) * 1995-10-20 1998-09-15 Hodosh; Milton Fluid dispensing apparatus
US6159161A (en) * 1995-10-20 2000-12-12 Hodosh; Milton Microprocessor-controlled fluid dispensing apparatus
US5800405A (en) 1995-12-01 1998-09-01 I-Flow Corporation Syringe actuation device
ZA9610374B (en) 1995-12-11 1997-06-23 Elan Med Tech Cartridge-based drug delivery device
CZ294332B6 (cs) 1996-03-19 2004-12-15 I-Flow Corporation Pumpa pro vypuzování infuzní tekutiny ze zásobníku
US5851197A (en) 1997-02-05 1998-12-22 Minimed Inc. Injector for a subcutaneous infusion set
US6003736A (en) * 1997-06-09 1999-12-21 Novo Nordisk A/S Device for controlled dispensing of a dose of a liquid contained in a cartridge
US6019747A (en) * 1997-10-21 2000-02-01 I-Flow Corporation Spring-actuated infusion syringe
US6019750A (en) 1997-12-04 2000-02-01 Baxter International Inc. Sliding reconstitution device with seal
JP3356679B2 (ja) * 1998-03-19 2002-12-16 日本サーボ株式会社 輸液装置
JP4425465B2 (ja) 1998-03-23 2010-03-03 エラン コーポレーション ピーエルシー 薬剤送給装置
US5919167A (en) * 1998-04-08 1999-07-06 Ferring Pharmaceuticals Disposable micropump
DE19840992A1 (de) 1998-09-08 2000-03-09 Disetronic Licensing Ag Drucküberwachung eines bei einer Infusion oder Injektion dosiert zu verabreichenden Produktfluids
US6022339A (en) 1998-09-15 2000-02-08 Baxter International Inc. Sliding reconstitution device for a diluent container
US6248093B1 (en) 1998-10-29 2001-06-19 Minimed Inc. Compact pump drive system
US6645177B1 (en) * 1999-02-09 2003-11-11 Alaris Medical Systems, Inc. Directly engaged syringe driver system
USD430289S (en) 1999-07-30 2000-08-29 Breg, Inc. Infusion pump for administering a fluid medication
DE60037531T2 (de) 1999-10-22 2008-12-11 ANTARES PHARMA, Inc., Minneapolis Medikamentenkartusche und injektionsvorrichtung
US7063684B2 (en) 1999-10-28 2006-06-20 Medtronic Minimed, Inc. Drive system seal
USD457949S1 (en) 2000-01-11 2002-05-28 John Andrew Krug Multiple chamber infusion pump
GB0006871D0 (en) * 2000-03-21 2000-05-10 Wymark Ltd A lubricating device
AUPQ867900A0 (en) 2000-07-10 2000-08-03 Medrad, Inc. Medical injector system
JP3458833B2 (ja) 2000-08-02 2003-10-20 双葉電子工業株式会社 蛍光表示管
US6537251B2 (en) * 2000-10-05 2003-03-25 Novo Nordisk A/S Medication delivery device with bended piston rod
DE60132507T2 (de) 2000-11-09 2008-12-24 Insulet Corp., Beverly Gerät zur transkutanen Abgabe von Medikamenten
WO2002071843A1 (fr) 2001-03-14 2002-09-19 Genteric, Inc. Transfert de gene par mediation de virus recombine adeno-associe via une infusion retroductale de virions
DK3210637T3 (da) 2001-04-06 2021-04-06 Hoffmann La Roche Infusionssæt
WO2002083209A1 (fr) * 2001-04-13 2002-10-24 Nipro Diabetes Systems Systeme de commande pour une pompe a perfusion
US20040236284A1 (en) 2001-06-08 2004-11-25 Hoste Shannon Marie-Lynn Needle hiding assembly for a medication injector
USD461241S1 (en) 2001-07-31 2002-08-06 Medtronic Minimed, Inc. Infusion pump for delivery of fluid
US20030055380A1 (en) 2001-09-19 2003-03-20 Flaherty J. Christopher Plunger for patient infusion device
US6830562B2 (en) 2001-09-27 2004-12-14 Unomedical A/S Injector device for placing a subcutaneous infusion set
US7611503B2 (en) 2004-04-16 2009-11-03 Medrad, Inc. Fluid delivery system, fluid path set, sterile connector and improved drip chamber and pressure isolation mechanism
US8048031B2 (en) 2001-10-26 2011-11-01 Retractable Technologies, Inc. IV catheter introducer
EP2319563B1 (fr) 2001-12-13 2013-05-29 Panasonic Corporation Instrument d'administration à usage médical
US8066678B2 (en) 2001-12-17 2011-11-29 Bard Access Systems, Inc. Safety needle with collapsible sheath
US6786890B2 (en) * 2002-01-25 2004-09-07 Novo Nordisk A/S Linear actuator and a medical delivery device comprising such linear actuator
US7033338B2 (en) 2002-02-28 2006-04-25 Smiths Medical Md, Inc. Cartridge and rod for axially loading medication pump
US20030199816A1 (en) 2002-04-17 2003-10-23 Scott Ramming Pre-loaded multi-chamber syringe
AU2003233504A1 (en) * 2002-05-24 2003-12-12 Eli Lilly And Company Medication injecting apparatus with fluid container piston-engaging drive member having internal hollow for accommodating drive member shifting mechanism
US20080132842A1 (en) 2002-06-06 2008-06-05 Flaherty J Christopher Plunger assembly for patient infusion device
US7036684B1 (en) 2002-06-13 2006-05-02 Hantman Ken S Diagonally divided bottle with curved line of division distinct from edge curve
US7250037B2 (en) 2002-07-22 2007-07-31 Becton, Dickinson And Company Patch-like infusion device
US20040039344A1 (en) 2002-08-22 2004-02-26 Baldwin Brian Eugene System, method and apparatus for administering medical liquids
DE10240165A1 (de) 2002-08-30 2004-03-18 Disetronic Licensing Ag Vorrichtung zum dosierten Ausstoßen eines flüssigen Wirkstoffes und Infusionspumpe
US20060069355A1 (en) * 2002-10-15 2006-03-30 Jared Alden Judson And Kenneth Alan Ritsher Medication dispensing apparatus with squeezable actuator
CA2501724C (fr) 2002-10-16 2011-07-19 Abbott Laboratories Procede pour etablir la distinction entre les etats de fonctionnement dans une pompe medicale
US7125396B2 (en) 2002-12-30 2006-10-24 Cardinal Health 303, Inc. Safety catheter system and method
DE10300896A1 (de) 2003-01-13 2004-07-22 Disetronic Licensing Ag Automatische, von Hydrogelen getriebene Fördereinrichtung mit einstellbarer Abgabecharakteristik zum Fördern eines Mediums, insbesondere Insulin
DE602004005597T2 (de) 2003-07-08 2008-02-14 Novo Nordisk A/S Tragbares medikamentenabgabegerät mit einer eingekapselten nadel
US20050033232A1 (en) 2003-08-05 2005-02-10 Kriesel Marshall S. Infusion apparatus with modulated flow control
WO2005037350A2 (fr) 2003-10-21 2005-04-28 Novo Nordisk A/S Raccord de fluide interne
DE10351594A1 (de) 2003-11-05 2005-06-16 Tecpharma Licensing Ag Vorrichtung für die Verabreichung eines injizierbaren Produkts
WO2005110194A1 (fr) * 2004-05-14 2005-11-24 Olympus Corporation Dispositif d'insertion
US7398802B2 (en) * 2004-09-02 2008-07-15 Baker James W System for dispensing biological fluids
EP1704886B1 (fr) 2005-03-24 2008-02-06 Disetronic Licensing AG Dispositif pour la distribution dosée d'un produit fluide
FR2884721A1 (fr) 2005-04-20 2006-10-27 Becton Dickinson France Soc Pa Ensemble d'injection et dispositif d'assistance a l'injection
US7905868B2 (en) * 2006-08-23 2011-03-15 Medtronic Minimed, Inc. Infusion medium delivery device and method with drive device for driving plunger in reservoir
US20080097291A1 (en) 2006-08-23 2008-04-24 Hanson Ian B Infusion pumps and methods and delivery devices and methods with same
CN101227943B (zh) * 2005-07-27 2010-12-15 诺沃-诺迪斯克有限公司 用于限制对应于剩余药品量的剂量设定的注射设备的剂量机构
WO2007038060A2 (fr) 2005-09-26 2007-04-05 M2 Medical A/S Fonctionnement d'un systeme de pompe a perfusion
US8057436B2 (en) 2005-09-26 2011-11-15 Asante Solutions, Inc. Dispensing fluid from an infusion pump system
US7534226B2 (en) * 2005-09-26 2009-05-19 M2 Group Holdings, Inc. Dispensing fluid from an infusion pump system
DE102005060928A1 (de) 2005-12-20 2007-06-28 Tecpharma Licensing Ag Injektionsvorrichtung mit axial überlappendem Dosier- oder Anzeigeglied
DE602006019153D1 (de) 2005-12-23 2011-02-03 Unomedical As Injektionsvorrichtung
NZ589864A (en) 2006-03-29 2012-07-27 Intelliject Inc Apparatus for mixing and dispensing medicament with energy storage devices, typically plungers, for mixing and dispensing
US20090254026A1 (en) * 2006-05-04 2009-10-08 Novo Nordisk A/S Syringe Device Comprising a Motor Adapted for Filling an Injection Chamber
US7815603B2 (en) 2006-05-17 2010-10-19 Alcon Research, Ltd. Ophthalmic injection method
CN103316403B (zh) 2006-06-30 2017-05-24 艾伯维生物技术有限公司 自动注射装置
US7789857B2 (en) 2006-08-23 2010-09-07 Medtronic Minimed, Inc. Infusion medium delivery system, device and method with needle inserter and needle inserter device and method
DK2061536T3 (da) 2006-08-23 2012-02-06 Medtronic Minimed Inc Anlæg og fremgangsmåde til fyldning af beholdere og til udlevering af et infusionsmedium
EP2054109B1 (fr) 2006-08-24 2017-12-13 F. Hoffmann-La Roche AG Dispositif d'insertion pour des têtes d'insertion, en particulier pour des ensembles de perfusion
US20080152507A1 (en) 2006-12-21 2008-06-26 Lifescan, Inc. Infusion pump with a capacitive displacement position sensor
US7803134B2 (en) 2007-01-10 2010-09-28 Animas Corporation Syringe assembly and infusion pump assembly incorporating such
DE102007013838A1 (de) 2007-03-22 2008-09-25 Tecpharma Licensing Ag Injektionsvorrichtung mit zeitkonstantem Ausschüttsignal
USD564087S1 (en) 2007-04-02 2008-03-11 Medingo, Ltd. Drug delivery pump
USD585543S1 (en) 2007-04-19 2009-01-27 Medingo, Ltd. Drug delivery pump
CA2685808C (fr) 2007-04-30 2013-06-11 Medtronic Minimed, Inc. Introduction d'aiguille et raccord d'ecoulement de fluide pour un systeme d'administration de milieu d'infusion
US8323250B2 (en) 2007-04-30 2012-12-04 Medtronic Minimed, Inc. Adhesive patch systems and methods
US20100137802A1 (en) * 2007-05-11 2010-06-03 Ofer Yodfat Methods and appratus for monitoring rotation of an infusion pump driving mechanism
GB0709580D0 (en) * 2007-05-18 2007-06-27 Abbi Lab Ltd Infusion pump
JP5091313B2 (ja) 2007-06-13 2012-12-05 カルメル ファルマ アクチボラゲット レセプタクルへ流体を供給する装置
US8002752B2 (en) 2007-06-25 2011-08-23 Medingo, Ltd. Protector apparatus
ATE501749T1 (de) 2007-07-06 2011-04-15 Shl Group Ab Monoinjektor mit doppelfedern
JP2010535039A (ja) 2007-08-01 2010-11-18 アルコン リサーチ， リミテッド 使い捨て眼科用注射装置
GB2452286B (en) * 2007-08-29 2012-09-26 Cilag Gmbh Int Injection system
EP2200677A1 (fr) 2007-09-17 2010-06-30 ICU Medical, Inc. Dispositifs d'insertion pour dispositifs de perfusion
EP2190500B8 (fr) 2007-09-17 2016-08-10 vTitan Corporation Private Limited Pompes à perfusion de haute précision
JP5653217B2 (ja) * 2007-10-02 2015-01-14 メディモップ メディカル プロジェクツ、エル・ティー・ディー 外部薬剤ポンプ
US7967795B1 (en) 2010-01-19 2011-06-28 Lamodel Ltd. Cartridge interface assembly with driving plunger
DE102007049446A1 (de) 2007-10-16 2009-04-23 Cequr Aps Katheter-Einführeinrichtung
RU2556965C2 (ru) 2008-01-23 2015-07-20 Ново Нордиск А/С Устройство для инъекции установленной дозы жидкого лекарственного средства
US20090204077A1 (en) 2008-02-13 2009-08-13 Hasted Soren B Moulded Connection Between Cannula and Delivery Part
US20110098652A1 (en) 2008-02-13 2011-04-28 Unomedical A/S Moulded Connection between Cannula and Delivery Part
US8540673B2 (en) 2008-03-18 2013-09-24 Calibra Medical, Inc. Disposable infusion device with actuation lock-out
USD586463S1 (en) 2008-04-01 2009-02-10 Smiths Medical Md, Inc. Ambulatory pump
US8568361B2 (en) 2008-04-09 2013-10-29 Medingo, Ltd. Modular skin-adherable system for medical fluid delivery
WO2009125582A1 (fr) * 2008-04-10 2009-10-15 パナソニック株式会社 Dispositif d'administration d'un médicament
US20090308895A1 (en) 2008-06-13 2009-12-17 Reynolds David L Rack and pinon drive for by-pass cartridge
US7927306B2 (en) 2008-06-26 2011-04-19 Calibra Medical, Inc. Disposable infusion device with prime indicator
GB0909130D0 (en) 2009-05-28 2009-07-01 L3 Technology Ltd Assay device
US8167844B2 (en) 2008-08-14 2012-05-01 Protectus Medical Devices, Inc. Safety IV needle/cannula introducer
GB2463034B (en) 2008-08-28 2012-11-07 Owen Mumford Ltd Autoinjection devices
BRPI0918297A2 (pt) 2008-09-10 2016-05-03 Hoffmann La Roche "dispositivo de distribuição de droga para bombear a medicação para dentro do corpo de um usuário"
WO2010030965A2 (fr) 2008-09-15 2010-03-18 Klein, David Injecteur indolore
US9370621B2 (en) 2008-12-16 2016-06-21 Medtronic Minimed, Inc. Needle insertion systems and methods
WO2010084113A1 (fr) 2009-01-20 2010-07-29 Novo Nordisk A/S Dispositif d'administration de médicament pourvu d'un réservoir comprenant une fenêtre qui peut être couverte par un magasin d'aiguilles
CA2965928C (fr) 2009-01-21 2018-10-23 Becton, Dickinson And Company Ensemble de perfusion
AU2010210158B2 (en) * 2009-02-05 2014-09-25 Sanofi-Aventis Deutschland Gmbh Medicament delivery devices
US9572927B2 (en) 2009-02-05 2017-02-21 Sanofi-Aventis Deutschland Gmbh Medicament delivery devices
DE202009001836U1 (de) 2009-02-13 2009-05-20 Dieter Hölzle Technik-Projekte GmbH Elektromechanische Injektionsvorrichtung
SE0900371A1 (sv) * 2009-03-24 2010-09-25 Istvan Bartha Anordning för distribution av flytande läkemedel
CA2757136A1 (fr) 2009-03-31 2010-10-07 Sanofi-Aventis Deutschland Gmbh Ameliorations concernant des dispositifs d'administration de medicament
CA2757134A1 (fr) * 2009-03-31 2010-10-07 Sanofi-Aventis Deutschland Gmbh Ameliorations concernant des dispositifs d'administration de medicament
DK2414011T3 (da) * 2009-04-01 2016-05-09 Shl Group Ab Medikamentafgivelsesindretning
USD629503S1 (en) 2009-05-08 2010-12-21 Sean Caffey Implantable drug-delivery pump
TW201109057A (en) 2009-06-02 2011-03-16 Sanofi Aventis Deutschland Medicated module with bypass and needle guard
JP5636645B2 (ja) 2009-07-03 2014-12-10 ニプロ株式会社 薬液移送装置
DE202009009602U1 (de) 2009-07-15 2009-12-10 B. Braun Melsungen Ag Kathetervorrichtung mit Nadelschutz
JP2011045537A (ja) 2009-08-27 2011-03-10 Nipro Corp 挿入装置用補助器具
US8157769B2 (en) 2009-09-15 2012-04-17 Medimop Medical Projects Ltd. Cartridge insertion assembly for drug delivery system
KR101868765B1 (ko) 2009-10-13 2018-06-18 발레리타스 인코포레이티드 유체 전달 장치
US9039653B2 (en) 2009-12-29 2015-05-26 Medtronic Minimed, Inc. Retention systems and methods
US8998858B2 (en) 2009-12-29 2015-04-07 Medtronic Minimed, Inc. Alignment and connection systems and methods
WO2011101381A2 (fr) * 2010-02-22 2011-08-25 Sanofi-Aventis Deutschland Gmbh Boîte de vitesse
WO2011101831A2 (fr) 2010-02-22 2011-08-25 Sulur Subramaniam Vanangamudi Crème médicinale à base d'acide fusidique préparée avec du fusidate de sodium et incorporant un biopolymère, un corticostéroïde - du butyrate de clobétasone, et un antifongique - du chlorhydrate de terbinafine, et son procédé de fabrication
JP5855022B2 (ja) * 2010-02-22 2016-02-09 サノフィ−アベンティス・ドイチュラント・ゲゼルシャフト・ミット・ベシュレンクテル・ハフツング 自動注射器用の動力伝達配置
WO2011121023A1 (fr) 2010-03-30 2011-10-06 Unomedical A/S Dispositif médical
CN103108665A (zh) 2010-04-20 2013-05-15 迷你泵有限责任公司 电解驱动药物泵装置
NZ702172A (en) 2010-04-21 2016-03-31 Abbvie Biotechnology Ltd Wearable automatic injection device for controlled delivery of therapeutic agents
DK3028726T3 (da) 2010-05-20 2019-07-29 Becton Dickinson Co Medicindispenser
USD669165S1 (en) 2010-05-27 2012-10-16 Asante Solutions, Inc. Infusion pump
TWM404020U (en) 2010-06-24 2011-05-21 Feng-Chyi Duh Active device for intravenous infusion
EP2608825B1 (fr) * 2010-08-27 2014-08-13 Novo Nordisk A/S Dispositif pour injection médicale
WO2012032411A2 (fr) 2010-09-07 2012-03-15 Tecpharma Licensing Ag Dispositif d'injection automatique
US9381300B2 (en) 2010-09-24 2016-07-05 Perqflo, Llc Infusion pumps
EP2433663A1 (fr) 2010-09-27 2012-03-28 Unomedical A/S Système d'insertion
US8474332B2 (en) 2010-10-20 2013-07-02 Medtronic Minimed, Inc. Sensor assembly and medical device incorporating same
US8795234B2 (en) 2010-11-30 2014-08-05 Becton, Dickinson And Company Integrated spring-activated ballistic insertion for drug infusion device
EP2468338A1 (fr) * 2010-12-21 2012-06-27 Sanofi-Aventis Deutschland GmbH Auto-injecteur
CN102526833B (zh) * 2010-12-30 2014-01-01 上海交通大学医学院附属瑞金医院 输液泵
US8945068B2 (en) 2011-02-22 2015-02-03 Medtronic Minimed, Inc. Fluid reservoir having a fluid delivery needle for a fluid infusion device
GB2488579A (en) 2011-03-02 2012-09-05 Owen Mumford Ltd Autoinjector with "injection complete" indicator
WO2012131044A1 (fr) 2011-03-30 2012-10-04 Unomedical A/S Dispositif d'introduction par voie sous-cutanée d'un dispositif médical
EP2537546A1 (fr) 2011-06-21 2012-12-26 Sanofi-Aventis Deutschland GmbH Dispositif d'administration de médicaments doté d'un mécanisme de contrôle de dose
CA2845367C (fr) 2011-09-02 2019-09-17 Unitract Syringe Pty Ltd Mecanisme d'entrainement pour des pompes d'administration de medicaments a indication integree de l'etat
US9814832B2 (en) 2011-09-02 2017-11-14 Unl Holdings Llc Drive mechanism for drug delivery pumps with integrated status indication
EP3415187B1 (fr) 2011-09-02 2020-08-26 UNL Holdings LLC Mécanisme d'insertion pour pompe d'administration de médicament
US11173244B2 (en) 2011-09-02 2021-11-16 Unl Holdings Llc Drive mechanism for drug delivery pumps with integrated status indication
US9707335B2 (en) 2011-09-02 2017-07-18 Unitract Syringe Pty Ltd Drive mechanism for drug delivery pumps with integrated status indication
JP2014528791A (ja) 2011-09-13 2014-10-30 ユニトラクト シリンジ プロプライエタリイ リミテッドＵｎｉｔｒａｃｔ Ｓｙｒｉｎｇｅ Ｐｔｙ Ｌｔｄ 薬剤送達ポンプ用の薬剤容器に対する滅菌流体経路接続部
US20140231427A1 (en) 2011-10-13 2014-08-21 Advanced Technology Materials, Inc. Liner-based shipping and dispensing containers for the substantially sterile storage, shipment, and dispense of materials
US8603027B2 (en) 2012-03-20 2013-12-10 Medtronic Minimed, Inc. Occlusion detection using pulse-width modulation and medical device incorporating same
US9463280B2 (en) 2012-03-26 2016-10-11 Medimop Medical Projects Ltd. Motion activated septum puncturing drug delivery device
USD697204S1 (en) 2012-03-30 2014-01-07 Antisense Pharma Gmbh Pump for pharmaceutical and cosmetics products
US10251995B2 (en) * 2012-04-10 2019-04-09 Shl Medical Ag Infusion device
USD684685S1 (en) 2012-04-13 2013-06-18 Becton, Dickinson And Company Infusion device button
USD685083S1 (en) 2012-04-13 2013-06-25 Becton, Dickinson And Company Infusion device
USD684686S1 (en) 2012-04-13 2013-06-18 Becton, Dickinson And Company Infusion device button
EP2838587B1 (fr) 2012-04-20 2016-03-09 Novo Nordisk A/S Dispositif d'injection médicale
BR112015003694A2 (pt) 2012-08-29 2017-07-04 Unitract Syringe Pty Ltd mecanismo de acionamento de entrega controlada e bomba de entrega de fármaco com entrega de fármaco controlada
USD745142S1 (en) 2012-08-30 2015-12-08 Unitract Syringe Pty Ltd Drug delivery pump
US9522223B2 (en) 2013-01-18 2016-12-20 Medtronic Minimed, Inc. Systems for fluid reservoir retention
DK2948205T3 (en) 2013-01-25 2018-02-05 Unl Holdings Llc DRIVE MECHANISM FOR PHARMACEUTICAL DISPENSER PUMPS WITH INTEGRATED STATUS INDICATOR
EP3756704B1 (fr) 2013-01-25 2022-05-11 UNL Holdings LLC Raccordement de trajet de fluide à opercule coulissant intégré et récipients pour médicaments pour pompes d'administration de médicaments
USD723157S1 (en) 2013-03-12 2015-02-24 Unitract Syringe Pty Ltd Drug delivery pump
US9308321B2 (en) * 2013-02-18 2016-04-12 Medtronic Minimed, Inc. Infusion device having gear assembly initialization
WO2015031714A1 (fr) 2013-08-30 2015-03-05 Covidien Lp Pompe de nutrition entérale équipée d'un système de chasse d'ensemble de pompe et pourvue d'une compensation de débit
CN110652628B (zh) 2013-12-06 2021-06-29 尤尼特拉克特注射器控股有限公司 用于具有整合式状态指示的药物投递泵的驱动机构
CN104751392A (zh) 2013-12-25 2015-07-01 昆达电脑科技(昆山)有限公司 医疗管理方法
USD752442S1 (en) 2014-06-09 2016-03-29 Bath & Body Works Brand Management, Inc. Bottle
WO2016049501A1 (fr) 2014-09-26 2016-03-31 Unitract Syringe Pty Ltd Récipients de médicament à tube concentrique et pompes d'administration de médicament permettant le mélange et l'administration
EP3439715B1 (fr) 2016-04-08 2021-03-10 Amgen Inc. Dispositif d'administration de médicament
US10695487B2 (en) 2016-08-30 2020-06-30 Unl Holdings Llc Controlled delivery drive mechanisms for drug delivery pumps
CA3074354A1 (fr) 2017-08-30 2019-03-07 Unl Holdings Llc Mecanismes d'entrainement d'administration commandee pour pompes d'administration de medicament

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None *

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DK3028727T3 (en) 2017-09-04
US20150217045A1 (en) 2015-08-06
US20150209505A1 (en) 2015-07-30
JP6645829B2 (ja) 2020-02-14
WO2014036308A2 (fr) 2014-03-06
JP6355169B2 (ja) 2018-07-11
PT2890431T (pt) 2017-02-21
IL236995A0 (en) 2015-03-31
JP2015526253A (ja) 2015-09-10
KR20150048834A (ko) 2015-05-07
PT2890432T (pt) 2017-09-12
IL236995B (en) 2019-11-28
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JP6388409B2 (ja) 2018-09-12
US9987419B2 (en) 2018-06-05
CA2881305A1 (fr) 2014-03-06
DK2890433T3 (da) 2020-01-27
IL236997B (en) 2019-11-28
EP3028727B1 (fr) 2017-05-10
ES2637229T3 (es) 2017-10-11
CN104582755A (zh) 2015-04-29
CA2881305C (fr) 2021-05-04
US11135356B2 (en) 2021-10-05
EP2890433A2 (fr) 2015-07-08
US10251996B2 (en) 2019-04-09
CA2881306A1 (fr) 2014-03-06
EP2890432A2 (fr) 2015-07-08
BR112015003422A2 (pt) 2018-04-17
JP2018196761A (ja) 2018-12-13
KR20150048832A (ko) 2015-05-07
US20150297827A1 (en) 2015-10-22
EP2890433B1 (fr) 2019-10-16
CN104602733A (zh) 2015-05-06
US10092693B2 (en) 2018-10-09
KR20150050580A (ko) 2015-05-08
AU2013308655B2 (en) 2018-03-01
CN104640584A (zh) 2015-05-20
WO2014036308A3 (fr) 2014-07-24
EP2890431A2 (fr) 2015-07-08
IL236997A0 (en) 2015-03-31
MX352388B (es) 2017-11-22
US20180243502A1 (en) 2018-08-30
EP3225265A1 (fr) 2017-10-04
EP3028727A1 (fr) 2016-06-08
HK1211885A1 (en) 2016-06-03
EP3210636B1 (fr) 2021-02-17
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DK2890431T3 (en) 2017-04-03
MX354141B (es) 2018-02-14
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JP2018167117A (ja) 2018-11-01
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BR112015003694A2 (pt) 2017-07-04
AU2013308699A1 (en) 2015-03-19
ES2639096T3 (es) 2017-10-25
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IL236958B (en) 2019-11-28
CN104640584B (zh) 2018-04-27
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CN104602733B (zh) 2018-04-27
AU2013308699B2 (en) 2018-03-01
MX2015002662A (es) 2015-05-12
WO2014036285A3 (fr) 2014-07-03
HK1218725A1 (zh) 2017-03-10
CA2881839A1 (fr) 2014-03-06
ES2615903T3 (es) 2017-06-08
US10933189B2 (en) 2021-03-02
WO2014036239A2 (fr) 2014-03-06
PT2890433T (pt) 2020-01-15
US20180304006A1 (en) 2018-10-25
IL236958A0 (en) 2015-03-31
AU2013308678B2 (en) 2018-01-04
AU2013308678A1 (en) 2015-03-19
JP2015530151A (ja) 2015-10-15
CN104582755B (zh) 2017-12-01
WO2014036285A2 (fr) 2014-03-06

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